Health monitoring systems and methods

ABSTRACT

Systems, methods and devices for reducing noise in health monitoring including monitoring systems, methods and/or devices receiving a health signal and/or having at least one electrode and/or sensor for health monitoring.

BACKGROUND

Advances in software, electronics, sensor technology and materialsscience have revolutionized patient monitoring technologies. Inparticular, many devices and systems are becoming available for avariety of health monitoring applications. However, improvements may yetbe desired for health monitoring devices and systems that provide one ormore of effective data collection and/or manipulation for parameterdetermination.

Further alternatives for patients and their physicians may then bedeveloped to include robust and convenient monitors that in someinstances may collect and transfer short-term or long-term data and/ormonitor events in real-time, and in some cases may includemulti-variable parameter determination.

SUMMARY

Described herein are several alternative medical monitoring devices,systems and/or methods for parameter determination, in some instancesfor long-term sensing and/or recording of cardiac and/or respiratoryand/or temperature data of one or more individuals, such as a neonate,infant, mother/parent, athlete, or patient. A number of alternativeimplementations and applications are summarized and/or exemplifiedherein below and throughout this specification.

In one alternative aspect, the developments hereof may include animplementation wherein a health device is configured for monitoring oneor a plurality of physiological parameters of one or more individualsfrom time-concordant measurements collected by one or a plurality ofsensors, including one or a variety of one or more of, but not limitedto, electrodes for measuring ionic potential changes forelectrocardiograms (ECGs), and/or one or more light sources and one ormore photodetectors, in some cases including LED-photodiode pairs, foroptically based oxygen saturation measurements, and/or one or moretemperature sensors, and/or one or more xyz accelerometers for movementand exertion measurements, and the like. In some implementations,methods and devices of the developments hereof may be used to generate arespiration waveform. Other implementations may include a circuit thatmimics a driven right-leg circuit (sometimes referred to herein as “aproxy driven right-leg circuit”) that may permit reduction in commonmode noise in a small-footprint device conveniently adhered or havingthe capacity to be adhered to an individual.

In another alternative aspect hereof, a blood pressure determination mayin some cases be made from a determination of pulse transit time. Thepulse transit time is the time for the cardiac pressure wave to travelfrom the heart to other locations in the body. Measurements of pulsetransit time may then be used to estimate blood pressure. Heart beattiming from ECG or otherwise and photoplethysmogram (aka PPG) signalscan be used to generate pulse transit time. Note, such signals may begenerated from conventional or other to-be-developed processes and/ordevices or systems; or, such signals may be taken from one or morewearable health monitoring devices such as those also describedhereinbelow.

In another alternative aspect, the developments hereof may include insome instances one or more methods and/or devices for measuring and/ordetermining oxygen saturation parameters from time concordant pulseoximetry signals and ECG signals. In some implementations, ECG signalsmay be used to define intervals, or “frames” of pulse oximetry data thatare collected and averaged for determining the constant and mainperiodic components (e.g., DC and AC components) of the pulse oximetrysignals from which, in turn, values for oxygen saturation may bedetermined. Patient-wearable devices of such implementations with pulseoximetry and ECG sensors may be particularly useful when placed on apatient's chest for such signal acquisition.

These as well as other alternative and/or additional aspects areexemplified in a number of illustrated alternative and/or additionalimplementations and applications, some of which are shown in the figuresand characterized in the claims section that follows. However, as willbe understood by the ordinarily skilled artisan, the above summary andthe detailed description below do not describe the entire scope of theinventions hereof and are indeed not intended to describe eachillustrated embodiment or every possible implementation of the presentinventions nor provide any limitation on the claims or scope ofprotection herein set forth below.

BRIEF DESCRIPTION OF THE DRAWINGS

The drawings include:

FIG. 1, which includes and is defined by sub-part FIGS. 1A-1R,illustrates several alternatives of the present developments, includinga variety of isometric, top and bottom plan and elevational views ofdevices and alternative conductive adhesive structures.

FIG. 2, which includes and is defined by sub-part FIGS. 2A-2D, providescircuit diagrams of alternatives to, in FIGS. 2A-2C, a driven right legcircuit, and in FIG. 2D, pulse oximetry.

FIG. 3 is a flow chart including alternative methods of use.

FIG. 4 illustrates an exemplary computer system or computing resourceswith which implementations hereof may be utilized.

FIG. 5, which includes and is defined by sub-part FIGS. 5A-5D, providesalternative screenshots of alternative software implementationsaccording hereto.

FIGS. 6A and 6B illustrate features of one embodiment for measuringoxygen saturation using pulse oximetry signals and electrocardiogramsignals.

FIG. 6C is a flow chart showing steps of one embodiment for determiningoxygen saturation values.

FIGS. 6D and 6E illustrate an embodiment for determining depth ofrespiration values.

FIGS. 7A, 7B and 7C set forth flow diagrams for alternativemethodologies hereof.

DETAILED DESCRIPTION

While the inventions hereof are amenable to various modifications andalternative forms, specifics hereof have been shown herein by way ofnon-limitative examples in the drawings and the following description.It should be understood, however, that the intention is not to limit theinventions to the particular embodiments described. The intention is tocover all modifications, equivalents, and alternatives falling withinthe spirit and scope of the inventions whether described here orotherwise being sufficiently appreciable as included herewithin even ifbeyond the literal words or figures hereof

In one aspect, a system hereof may include a device for monitoringphysiological parameters such as one or more or all of electrocardiogram(aka ECG or EKG), photoplethysmogram (aka PPG), pulse oximetry,temperature and/or patient acceleration or movement signals.

Moreover, systems hereof may be established to measure and/or processsuch signals of a patient using or including any one or more of thefollowing elements: (a) a circuit, sometimes flexible as in or on orforming a flexible or flex circuit board, embedded in or on a flatelastic substrate or board having a top surface and a bottom surface,the circuit having one or more of (i) at least one sensor mounted in oron or adjacent the bottom surface of the flat elastic substrate, the atleast one sensor being capable of electrical or optical communicationwith the patient. In some implementations, a circuit may include (ii) atleast one signal processing module for receiving and/or acceptingsignals from the at least one sensor in some implementations alsoproviding for transforming such signals for storage as patient data;and/or (iii) at least one memory module for receiving and/or acceptingand storing patient data, and/or (iv) at least one data communicationmodule for transferring patient data, stored or otherwise to an externaldevice, and/or (v) a control module for controlling the timing andoperation of the at least one sensor, one or more of the at least onesignal processing module, the at least one memory module, the at leastone data communication module, and/or the control module capable ofreceiving commands to implement transfer of patient data by the at leastone data communication module and to erase and/or wipe patient data fromthe at least one memory module. In some implementations, a system hereofmay include (b) a conductive adhesive removably attached to the bottomsurface of the flat elastic substrate, the conductive adhesive capableof adhering to skin of the patient or other user and in somenon-limiting examples a system hereof may be capable of conducting anelectrical signal substantially only in a direction perpendicular to thebottom surface of the flat elastic substrate, and/or in someimplementations may include a conductive portion adjacent the sensor orsensors and a non-conductive portion. In some implementations, theconductive adhesive is an anisotropically conductive adhesive in that itcomprises regions of material that conducts current substantially onlyin a direction perpendicular to the skin (i.e. “z-axis” conduction).

In some implementations, devices hereof will be for comprehensivelong-term cardiac monitoring, inter alia. Features of such may but notnecessarily include any one or more of a Lead 1 ECG, PPG, pulseoximeter, accelerometer, temperature sensor and/or a button or otherindicator for manual patient event marking. Such a device may be adaptedto store up to, for example, about two weeks of continuous data (thoughmore or less will also be feasible in alternative implementations),which may in some implementations be downloaded to a clinic or othercomputer in a short time period, as for one example, in only about 90seconds (though more or less time will be viable in alternativeimplementations) via computer connection, whether wireless or wired asin one example by USB or other acceptable data connection. A companionsoftware data analysis package may be adapted to provide automated eventcapture and/or allow immediate or delayed, local data interpretation.

Intermittent cardiac anomalies are often difficult for physicians todetect and/or diagnose, as they would typically have to occur during aphysical examination of the patient. A device hereof may address thisproblem with what in some implementations may be a continuous orsubstantially continuous monitoring of one or a number of vital signs.

Some alternative features may include but not be limited to one or moreof (i) a driven “Right Leg” circuit with electrodes located only on thechest, and/or (ii) a “z-Axis” or anisotropic conductive adhesiveelectrode interface that may permit electrical communication onlybetween an electrode and a patient's skin immediately beneath theelectrode, and/or (iii) data transmission to and interpretation by alocal computer accessible to CCU/ICU personnel, and/or (iv) a uniquecombination of hardware that may allow correlation of multiple datasources in time concordance to aid in diagnosis.

In some alternative non-limiting implementations, devices and systemshereof may provide 1) reusability (in some cases near or greater thanabout 1000 patients) that may allow recouping cost of the device in justabout 10-15 patient tests; and/or 2) one or more of ECG waveform data,inertial exertion sensing, manual event marking, temperature sensingand/or pulse oximetry, any one or all of which in time concordance tobetter detect and analyze arrhythmic events; and/or 3) efficientwatertightness or waterproofing (for the patient/wearer to be able toswim while wearing the device); and/or 4) a comprehensive analysispackage for typically immediate, local data interpretation. Analternative device may be adapted to take advantage of flex-circuittechnology, to provide a device that is light-weight, thin, durable, andflexible to conform to and move with the patient's skin duringpatient/wearer movement.

FIGS. 1 and 2 illustrate examples of alternative implementations ofdevices that may be so adapted.

FIG. 1, which is defined by and includes all of sub-part FIGS. 1A-1P,shows a device 100 that has a component side or top side 101, patientside or circuit side 102, and one or more inner electrical layer(s),generally identified by the reference 103 and an elongated strip layer105. The strip layer 105 may have electronics thereon and/ortherewithin. FIG. 1A shows isometrically these in what may in somenon-limitative implementations be considered a substantially transparentdevice together with some other elements that may be used herewith. FIG.1B is more specifically directed to a top side 101 plan view and FIG. 1Cto an underside, patient side 102 plan view and FIG. 1D a firstelevational, side view.

Many of the optional electronics hereof may be disposed in theelectronics layer or layers 103, and as generally indicated here, theelectronics may be encapsulated in a material 104 (see FIGS. 1A, 1B, 1Dand 1K for some examples, and see FIGS. 1N, 1O, 1P and 1Q describedfurther below, e.g.), medical grade silicone, plastic or the like, orpotting material, to fix them in operative position on or in orotherwise functionally disposed relative to the elongated strip layer105. The potting or other material may in many implementations also oralternatively provide a waterproof or watertight or water resistantcoverage of the electronics to keep them operative even in water orsweat usage environments. One or more access points, junctions or otherfunctional units 106 may be provided on and/or through any side of theencapsulation material 104 for exterior access and/or communication withthe electronics disposed therewithin, or thereunder. FIGS. 1A, 1B and 1Dshow four such accesses 106 on the top side. These may include high Zdata communication ports and/or charging contacts, inter alia. Thisupper or component side 101 of device 100 may be coated in a siliconecompound for protection and/or waterproofing, with only, in someexamples, a HS USB connector exposed via, e.g., one or more ports 106,for data communication or transfer and/or for charging.

The elongated strip layer 105 may be or may include a circuit or circuitportions such as electrical leads or other inner layer conductors, e.g.,leads 107 shown in FIG. 1D, for communication between the electronics103 and the electrically conductive pads or contacts 108, 109 and 110described further below (108 and 109 being in some examples, highimpedance/high Z silver or copper/silver electrodes forelectrocardiograph, ECG, and 110 at times being a reference electrode).In many implementations, the strip layer 105 may be or may include flexcircuitry understood to provide acceptable deformation, twisting,bending and the like, and yet retain robust electrical circuitryconnections therewithin. Note, though the electronics 103 and electrodes108, 109, 110 are shown attached to layer 105; on top for electronics103, and to the bottom or patient side for electrodes 108, 109, 110; itmay be that such elements may be formed in or otherwise disposed withinthe layer 105, or at least be relatively indistinguishably disposed inrelative operational positions in one or more layers with or on oradjacent layer 105 in practice. Similarly, the leads or traces 107 areshown embedded (by dashed line representation in FIG. 1D); however,these may be on the top or bottom side, though more likely top side toinsulate from other skin side electrical communications. If initiallytop side (or bottom), the traces may be subsequently covered with aninsulative encapsulant or like protective cover (not separately shown),and/or in many implementations, a flexible material to maintain aflexible alternative for the entire, or majority of layer 105.

On the patient side 102, the ECG electrodes 108, 109 and 110 may be leftexposed for substantially direct patient skin contact (though likelywith at least a conductive gel applied therebetween); and/or, in manyimplementations, the patient side electrodes 108, 109 and/or 110 may becovered by a conductive adhesive material as will be described below.The electrodes may be plated with or may be a robust high conductivematerial, as for example, silver/silver chloride for biocompatibilityand high signal quality, and in some implementations may be highlyrobust and, for one non-limiting example, be adapted to withstand overabout one thousand (1000) alcohol cleaning cycles between patients.Windows or other communication channels or openings 111, 112 (FIG. 1C)may be provided for a pulse oximeter, for example, for LEDs and asensor. Such openings 111, 112 (e.g., FIG. 1C) would typically bedisposed for optimum light communication to and from the patient skin.An alternative disposition of one or more light conduits 111 a/112 a(and 111 b/112 b) is shown in a non-limiting example in FIG. 1D morenearly disposed and/or connected to the electronics 103. A variety ofalternative placements may be usable herein/herewith, some of whichfurther described below.

In some implementations, sampling of the ambient light (with the LEDsoff) may be provided, and then subtracting this from each of thepulse-ox signals in order to cancel out the noise caused by sunlight orother ambient light sources.

The LEDs and one or more photodiode sensors may also and/oralternatively be covered with a layer of silicone to remove any air gapbetween the sensor/LEDs and the patient skin. Some examples of such areset forth in respective FIGS. 1H and/or 1K and/or 1L and/or 1M and/or1N, 1O, 1P and 1Q; where a silicone layer or covering 121 and/or 121 aand/or 121 b and/or 121 c and/or 121 d is shown covering/surrounding thelight conduits and/or sensors/LEDs 111 c/111 d/112 c. LED 111 c (FIGS.1H and/or 1K and/or one or more of 1L, 1M, 1N, 1O, 1P and/or 1Q) mightbe a Red LED, LED 111 d (FIGS. 1H and/or 1K and/or one or more of 1L-1Q)might be an IR (infrared) LED and the device 112 c (FIGS. 1H and 1Kand/or one or more of 1L-1Q)) might be a sensor. Alternative and/oradditional LEDs might be provided; for a first example, one or moreadditional or alternative colors of LEDs (not shown) might be providednot unlike those shown in FIGS. 1H and/or 1K and/or one or more of1L-1Q, as for example a Green LED (not shown) for additional and/oralternative functionality as described further below.

Other alternative LED and sensor arrays or arrangements are shown inFIGS. 1L and 1M wherein one or more LEDs are more centrally disposedwithin epoxy/light-pipe 121 c on a substrate 105 a and one or moresensors or photodiodes are more peripherally disposed. In FIG. 1L twoLEDs 111 c and 111 d (not unlike LEDs 111 c and 111 d of FIGS. 1H and/or1K, but for positioning/geometry) are shown relatively centrallydisposed relative to one or more sensors, here, two sensors orphotodiodes 112 c and 112 d. As above-described for FIGS. 1H and/or 1K,LED 111 c might be a Red LED, and LED 111 d might be an IR (infrared)LED and the devices 112 c and/or 112 d might be one or more sensors,here two sensors or photodiodes 112 c and 112 d. In FIG. 1M, four LEDs111 c, 111 d, 111 e and 111 f (not unlike LEDs 111 c and 111 d of FIGS.1H and/or 1K and/or 1L, but for number, positioning and/or geometry) areshown relatively centrally disposed relative to one or more sensors,here, four sensors or photodiodes 112 c, 112 d, 112 e and 112 f. Asabove-described for FIGS. 1H and/or 1K and/or 1L, LED 111 c might be aRed LED, and LED 111 d might be an IR (infrared) LED, and/or 111 e mightalso be a Red LED, and LED 111 f might be an IR (infrared) LED and thedevices 112 c, 112 d, 112 e and/or 112 f might be one or more sensors,here four sensors or photodiodes 112 c, 112 d, 112 e and 112 f.

Placing the LEDs in the more centrally disposed positioning of FIGS. 1Land 1M and surrounding those more centrally disposed LEDs with sensorsor photodiodes, as opposed to the more or relatively conventional methodof a central sensor or photodiode surrounded by LEDs, provides ageometry that may be disposed to capture a much greater percentage ofthe emitted light, emitted from the LEDs. In the more or relativelyconventional geometry, substantially all of the emitted light facingaway from the photodiode is wasted. In the geometries of and/ordescribed for FIGS. 1L and 1M, much more light, perhaps as much asvirtually all of the emitted light may be captured by the sensors orphotodiodes, or in some cases, a significantly higher efficiency capturethan conventional. Due to the higher efficiency light capture, fewerLEDs might thus be required than conventional Multi-LED integratedsensors. This may contribute to significantly reducing power consumptionand yet achieve similar or better measurement results. In sum, ageometry of LEDs, such as the red and IR combinations described above,combined with an array of photodiodes (or sensors) is shown anddescribed that may enable a higher concentration of light into thesubcutaneous region of the subject(patient/infant/neonate/mother/athlete, e.g.). The combination of LEDsand photodiodes/sensors might also be referred to in someimplementations as a High-Efficiency Integrated Sensor. This arrangementmay be implemented in determination of SpO2 (peripheral capillary oxygensaturation). Note, in some practical implementations, the sensors shownin FIGS. 1L and 1M, e.g., may be about 5 mm² and the diameter of theexterior circle encompassing the sensors and LEDs might be acorresponding about 8 mm. In some implementations, it may be that about3.2 mm red may be set for a preferred distance from the center of thered LED light source to the center of the corresponding sensor orsensors, and may be a preferred distance of about 3.7 mm set from thecenter of the IR LED light source to the corresponding sensor or sensorstherefor.

This silicone layer or covering 121/121 a/121 b/121 c/121 d/121 e mayreduce the light lost to reflection off the skin, and thereby greatlyincrease the signal and reduce the noise caused by motion of the skinrelative to the sensor. In some implementations this silicone might bereferred to as a light pipe and in some situations may be clear,colorless, and/or medical grade silicone. As described further below,the silicone layer or covering 121 and/or 121 a and/or 121 b and/or 121c and/or 121 d and/or lens surface 121 e (sometimes referred to hereinin short by 121/121 a/121 b/121 c/121 d/121 e but having the samemeaning hereof) may also/alternatively be referred to as a light pipe orlens 121/121 a/121 b/121 c/121 d/121 e herein inasmuch as how it may beinvolved in light transmitting or to be transmitted therethrough,whether upon emission or received upon reflection or both.

In one or more implementations, an encapsulant and/or lens 121/121 a/121b/121 c/121 d/121 e hereof may be made from a medical grade siliconethat is one or more of clear, colorless, soft, low durometer. Exemplarsof such specialized silicones that may be used herewith are known as“tacky gels” (several suppliers), and typically have very high-tackadhesives, preferably embedded on both sides. A low durometer siliconecombined with double- sided adhesive on the tacky gel allows theconstruction of a lens 121/121 a/121 b/121 c/121 d/121 e that may beboth conforming to the electronic sensors and skin, as well as, in someimplementations, exhibiting properties of motion artifact reduction bylimiting movement between the skin-lens-sensor interface. A lensaccording hereto may also/alternatively be specially shaped such that itcan be trapped between layers of the composite adhesive strip (see e.g.,alternatives of FIGS. 1D, 1G and 1I and 1J), and in someimplementations, with a raised portion the size of the opening, often arectangular opening, in the adhesive strip that allows the lens toprotrude slightly on the patient side of the adhesive strip (see furtherdetail relative to FIG. 1K, described below).

In FIG. 1K an implementation of a further alternative silicone coveringor encapsulant 121 a for the LEDs and sensor 111 c/111 d/112 c, mayinclude a convex lens at or adjacent the covering external surface 121b. In many implementations, the external surface and lens are one andthe same and/or the lens may be defined by the surface 121 b of theencapsulant material 121 a. What this provides is a structure and methodfor interfacing pulse oximetry LED emitters 111 c/111 d and one or morephotodiode sensors 112 c with the skin surface, whether chest orforehead (e.g., infant or neonate) or otherwise mounted on the patientor user body.

More particularly, as otherwise described herein, a system and/or device100 hereof may utilize one or multiple LED emitters 111 c/111 d (and/or111 e and/or 111 f) of selected wavelengths and one or multiplephotodiode sensors. However, In order to maximize coupling of theLED/sensor combination to the skin 1001 of a wearer 1000, an encapsulantand/or lens 121/121 a/121 b/121 c/121 d/121 e comprised of opticallyclear, medical grade silicone may be molded onto or molded such that itmay be later attached in covering relationship on the LED/sensorcombination 111 c/111 d/112 c. In many implementations, as for examplein FIG. 1K, the lens 121 b may be partially spherical or perhapshemispherical in nature, though it need not be; see e.g., FIGS. 1N-1Q,described below. Curvature of other shapes may be useful as well.Curvature may reduce loss of skin contact when the device 100 may bemoved, whether by wearer motion or otherwise. I.e., motion of the wearer1000 or the device 100 relative to the wearer 1000 in FIG. 1K can resultin a quasi-rolling contact of the lens on and in relation to the skin1001. Better maintained skin contact means better data acquisitionwithout interruption and/or with reduced noise. In some implementations,including those above and below (though not directly shown therein,i.e., alternatively included or not included therewith), or as describedwith specific reference to FIG. 1Q below, a thin silicone adhesive 113 emay be used on and between the silicone layer 121/121 a/121 b/121 c/121d/121 e to assist with maintenance of the skin contact relative to thesilicone encapsulant 121/121 a/121 b/121 c/121 d/121 e. See descriptionof FIG. 1Q below, e.g.

Moreover, related to the function of maintaining contact is the lightpiping effect that may be achieved when LEDs and sensors, even ofdifferent heights are communicating substantially with little orsubstantially without air gap interruption through the light pipe of theencapsulant material 121 a/121 c/121 d/121 e from the emission to theskin and back from the skin to the sensors. With no air gap from emitterto and through the light pipe 121 a/121 c/121 d/121 e and/or sometimesincluding a curved surface 121 b substantially constant contact with theskin, there is thus no air gap or with little or substantially no airgap interruption in transmission into and through and reflected back onreturn from within the skin and back to the sensor via the same lightpipe material 121 a/121 c/121 d/121 e (transmission and reflection bothreferring to light travel). This reduces inefficiencies caused by lightwave scattering at air gap interfaces (air gaps allow for light tobounce off the skin or other surface). I.e., encapsulation of the LEDsand the sensor; provides no air-gap and a light pipe effect to and thecurved surface provides high quality low scattering transmission intothe skin and reception of reflection from the skin and bone. The lightpipe and curved lens surface maintain uninterrupted contact skin andlens reduces lost signals due skin reflection. The signal to noise ratiogoes down and data acquisition goes up in quality.

Such an encapsulant 121 a/121 c/121 d/121 e and/or a lens 121 b/121 emay thus serve one or multiple purposes, including in some instances,inter alia: 1) providing a “light-pipe” effect to assure equal orotherwise high quality coupling of the different height LEDs andsensors, as well as substantially constant coupling to the skin toreduce motion artifact; 2) focusing of emitted light through the skin tothe bone; and, 3) focusing of reflected light through the skin to thephotodiode sensors.

As a further note, for a curved lens 121 b option as from FIG. 1K, theradius of the lens may be designed to maximize 1) through 3). The heightof the lens may be designed to allow it to protrude above compositeadhesive 113 of the device 100 and into the skin, but not deep enough todisturb the capillary bed which would also result in bad data. Moreover,the radius of curvature and the angles of LED lightwave emission are notnecessarily highly controlled and need not be because the LEDs used topenetrate the skin, e.g., the red and infra-red and/or green LEDs;provide a very wide array of angles of emission, and thus a large numberof reflected array of lightwaves will be focused back to the sensor by alarge variety of curved surfaces. I.e., the curved surface is helpfulfor maintaining contact through movement (accidental or on purpose), andis less important to the angles of transmission through the skin andreflection back to the sensor. In other words, many different radii ofcurvature will be effective with very little difference in data/wavetransmission and reflection; the wide angle emission of LED takes careof what might be a variety of radii. Rather, the curvature may have morelimitation in the maintenance of contact due to movement of the device100—e.g., flatter curvatures won't roll readily, and very small radii ofcurvature will not transmit or receive as much data.

In some implementations, a radii of curvature found useful have beenbetween about 20 and 40 (both 20.34 mm and 39.94 mm radii of curvaturehave been found useful) for a device having LEDs and sensors in acompartment of about 12.6 mm by 6.6 mm. It may be noted further thatLEDs may be on one side or another or on two opposing sides or perhapsat four or more substantially equi-distant points around a sensor andmay provide desirable results.

Note further, pulse oximetry hereof may be with multiple light sourcesand/or sensors as may be one interpretation of the dispositions of FIGS.1H and 1K, and/or any one or more of 1L-1Q, e.g. Typical pulse oximetrycircuitry uses one light source (LED) per wavelength (typically red,infrared, and sometimes others including green or long time averages ofred/IR for further examples as described below). However, devices and/ormethods hereof may make use of multiple light sources for eachwavelength. This may allow for interrogation of a wider area ofcapillary bed in/on the patient/wearer in order to reduce the effects ofa local motion artifact. Similarly, multiple sensors may be used for thesame or similar purpose or advantage.

Furthermore, a combination of driven right leg and/or proxy driven rightleg together with pulse oximetry can provide additional benefits. Theright leg circuit, proxy right leg and/or driven right leg, whether forchest or forehead or other electrode placement, can remove common modeand power line noise that would/might otherwise be capacitively-coupledinto the pulse oximetry sensor and reduce effectiveness thereof. Acombination of driven right leg and/or proxy driven right leg andimproved pulse oximetry with a lens as described in and for FIG. 1Kand/or the light pipes of FIGS. 1H and/or any one or more of FIGS. 1L-1Qmay significantly reduce such noise, and thereby enhance dataacquisition. For driven electrodes see further detail below.

Thus, measurement of arterial blood oxygen content can be made usingoptical signals (sometimes also referred to as heart beat opticalsignals), typically from Red and Infra-Red pulsed sources, which exhibitdifferent optical absorptions dependent on oxy-haemoglobin presence orabsence. In sum, a transmissive system is used with light sources andoptical detectors. In many implementations as described following, alight pipe that encapsulates either or both the light source or sourcesand the one or more sensors may be employed, particularly a light pipeencapsulating, meaning having substantially no air gaps, may be used forproviding either or both increased efficiency in light emission to theskin and/or capturing otherwise lost photons upon collection.

Herein, reflective systems are typical, and these often have someadvantages being less intrusive, and perhaps being more portable. Asdescribed herein, such reflective systems typically employ a red and aninfra-red source and a photo-diode sensor or detector, or multiplearrangements of these components. Also as described, oneimplementation/method employs one or more central large areaphoto-diodes/sensors/detectors, with one or more LED sources, often oneor more of each of a red, and an infra-red LED sources adjacent to thephoto-diode or in an array around it. Also as described, an alternativearrangement uses a central LED set of one or more light sources, withone or more of each wavelength type (Red, InfraRed, Green, etc.), andmultiple large area photo-diodes or light sensors surrounding thecentral LEDs. Such an arrangement might use two or three or four suchdetectors around the LEDs to collect more light scattering from the LEDsthrough the skin and other tissues; see e.g., FIGS. 1L and/or 1M.

A further alternative implementation may employ structural enhancementsto and/or around the light sources and/or the one or multiplephoto-diodes. Described first are one or more such enhancements disposedin relation to the central LED arrangement described above, though thefollowing could be used with or relative to the prior described centralsensor arrangement as well. The optical enhancing structures may provideminimal intrusion in the collection area and may reduce photo-diodeareas or reduce numbers of photodiodes. Cost benefits and/or increasedefficiency may thus result.

In FIGS. 1N, 1O, 1P and 1Q, in the light pipe 121 d, the central LEDsources 111 c and 111 d are isolated from the peripheral photo-detectors112 c, 112 d, 112 e and 112 f on the substrate 105 a by asurroundingbarrier wall 122 (here also identified by the alternative reference B1).A further optional external barrier 123 surrounding the sensor area isalso shown. The barrier wall 122 (or B1) and/or wall 123 (or B2) is/orpreferably opaque and/or reflective to both red and IR (or to whateverother color or wavelength of light is being used, e.g., green etc.) inorder to prevent crosstalk between the LEDs and the sensors. i.e.,preferably want all of the light leaving the LED area to go into theskin rather than some of the light rays finding a path to enter thesensors directly. A preferable surface for the barrier would bediffuse-reflective (as opposed generally to relative absorptive and/ormirror-shiny). An example may be clear anodized aluminum. Another wouldbe textured white paint. Operation is shown and described relative toFIGS. 1P and/or 1Q; see below.

The shape and size of the wall 122 can be chosen appropriate to theshape and size of the LED sources, here sources 111 c and 111 d. Forexample, the wall 122 could be, as shown, a circle, or could be a squareor rectangular shape or otherwise (not shown) around the LEDs 111 c, 111d (noting here also that more or fewer light sources might be includedwithin or enclosed by the wall 122). The width or thickness of and thematerial used for the barrier wall 122 can be variable or varied asneeded or desired as well; indeed, the width may depend upon thematerial and/or vice versa in that the relative opacity of anyparticular material may mean less or more width necessary to provide aparticular level of opacity or relative diffuse reflectivity. Theparticular wavelengths of light, i.e., type of light used, and/or thetype or types of sensors and/or the relative and/or overall geometricalrelationships (sensors to light sources, sensors to sensors, and/orlight sources to light sources) may also figure into the relativedimensions and/or material used for and/or due to the relative opacityin relation to the particular wavelengths. There may be situations wherethe relative thicknesses may have more to do with the type of materialof the wall, or the opacity or relative diffuse reflectivity thereof. Insome implementations, the barrier/wall may be machined, anodizedaluminum, or other similar material, but other implementations are ofplastic, e.g., a molded plastic. For Red and Infra-Red usage, a drivingconsideration can be that the material would perhaps preferably beopaque or reflective or diffuse reflective to both 660 and 940nanometers. Thus, in many situations, very thin aluminum meets thiscriteria, and thicker plastic does as well.

The options for wall 122 will primarily be for the provision of anoptical barrier to sideways propagation of either the radiation from theLEDs (e.g., as here thus far, the Red or the Infra-Red light from, e.g.,LEDs 111 c/111 d), and the wall 122 is preferably level or slightlyhigher than the optical exit window of the LEDs. It is preferred thatthe barrier wall 122 also has a width sufficient to prevent opticalcrosstalk of light rays that never enter the skin or scatteringmaterial, but not so wide that light from the LEDs that is scatteredfrom the skin or other flesh material, is prevented from reaching thephoto-diode detectors outside the barrier wall.

An optional external barrier wall 123 might also be employed. This oneassisting with collection of light reflected from the patient or user.Similar considerations for size and thickness and material may beemployed with wall 123; the difference being primarily in collection asopposed to light generation.

Where these developments may provide improvement with external detectorsas described here, FIGS. 1N/1O, and/or 1P/1Q, is that an opticalcollecting structure is added that can collect light from other regionswhere detector diodes are not present, and conduct or reflect some ofthat radiation in such a way as to reach one or more of the detectors.Note, central detectors with otherwise separately isolated light sources(not shown) may also have similar improvements.

Preferred structures of this type may include a transparent opticalmedium, here the light pipe material 121 d. This light pipe material maybe molded into a shape within and/or surrounding the relatively opaquebarrier wall 122 (see e.g., FIG. 1Q, described further below), andcontain sources 111 c and 111 d (and/or others if/when present) withinthe wall 122 and/or contain outside the wall 122 (between wall 122 andwall 123) the diode detectors 112 c, 112 d, 112 e and/or 112 f (and/orothers if/when present) embedded in that structure 121 d with little orsubstantially no air gaps between the detectors and the light pipematerial. The detector devices 112 c, 112 d, 112 e and/or 112 f may bemolded into the optical medium, i.e., light pipe material, itself, orcould be inside premolded cavities in that optical medium. Opticalstructures of this type, could be generally referred to as “lightpipes”.

The shape of the light pipe structure 121 d and/or surface 121 e can bechosen in a variety of ways, depending on the number and size or shapeof the detector diodes, and may be designed in such a way as to capturescattered light received from the skin or flesh material not directly incontact or above any detector diode, and contain it by means of totalinternal reflection, and using scattering reflective surfaces, toredirect rays in a direction towards one or more of the photo diodes. Inthis way, light that would be lost in previous designs, is captured bydevices of these present implementations. In FIGS. 1N and 1O, the epoxy(light pipe) 121 d is relatively flat, i.e., presenting a relativelyflat surface 121 e, not concave or convex, though it may be thatcurvature will work with the barrier wall or walls hereof. In FIG. 1Q,also a relatively or substantially flat surface 121 e is shown.

Shown also in FIG. 1Q is an optional thin silicone adhesive 113 e onsurface 121 e which may be used to relatively adhere the device to theskin (not shown here) to reduce movement of the device relative to theskin and enhance light transmission and reception. If used, such anadhesive may preferably be as thin as operably possible so as not tointerfere with or provide refraction of light waves passingtherethrough. A 0.2 mm thickness may be so operable. Also, it may bethat a similar refractive index of the adhesive to theexpoxy/encapsulant/light pipe 121/121 a/121 b/121 c/121 d/121 e might bepreferred. This choosing of a similar refractive index may be ofassistance or may be related to thickness as well as material ofadhesive to be used. E.g., an appropriate refractive index similaritymay result from or lead to an operable 0.2 mm thickness.

FIGS. 1P and 1Q show some operative examples and/or alternatives. InFIG. 1P, where no light pipe is shown for simplicity, though could be anoperable alternative example, light wave emissions A, B and C are shownemanating from the exemplar LED 111 c. Wave A is a relative directemission meeting no obstacle on its way from the device to the skin (notshown), whereas wave B is shown as reflected off the wall 122 (notethough waves are sometimes described, it is understood that light energyin whatever form is intended herewithin, whether for example it is ormay better be understood as photons which are more particularly asunderstood as emitted and/or collected). Less preferred is a wave Cshown not reflected off wall 122; here shown merely for highlighting thepreference toward most if not all waves leaving the LED finding a way tobe reflected to exit the LED area and enter the skin of the user (notshown here). Light collection is shown relative to the exemplar sensors112 c and 112 d, where in FIG. 2P, relatively direct waves D are shownas they might enter the sensor area and be captured by the sensors 112 cand/or 112 d. Reflected waves E are also shown as they might bereflected off the walls 122 and/or 123. Note, the floor or top surfaceof the substrate 105 a might also be diffuse reflective to the waves andassist in reflecting these ultimately for sensor collection.

In FIG. 1Q, the light pipe/s 121 d are shown as is an optional thinadhesive 113 e. The relative refractive indices of these materials mayor may not affect, or largely affect the light passing therethrough.Preference is for similarity of refractive indices to minimizerefraction. Even so, some refraction may occur as shown for example byemitting light wave B in FIG. 1Q and in collected waves E and F, Fdiffering from E by not also being reflected of the walls 122 and/or 123as is light wave E. Light wave B is shown both reflected and refracted.Choice of materials and sizes and shapes of relative structures canassist in management of relative reflection and/or refraction towardincreasing efficiency in light emission and/or capture.

Returning to the adhesive alternatives, FIG. 1D provides a first exampleof an adhesive 113 that may be used herewith. The adhesive layer 113 ishere a double-sided adhesive for application to the bottom side 102 ofthe device 100, and a second side, perhaps with a different type ofadhesive for adhering to the skin of the human patient (not shown).Different types of materials for adhesion might be used in that thematerial of choice to which the adhesive layer is to be attached aredifferent; typically, circuit or circuit board material for connectionto the device 100, and patient skin (not separately shown) on thepatient side. A protective backing 114 may be employed on the patientside until application to the patient is desired. Note, in manyapplications, the adhesive 113 is anisotropic in that it may preferablybe only conductive in a single or substantially a single direction,e.g., the axis perpendicular to the surface of adhesive contact. Thus,good electrically conductive contact for signal communication can be hadthrough such adhesive to/through the adhesive to the electrical contactsor electrodes, 108, 109 and 110. Note, a corresponding one or more lightapertures 111 b/112 b are shown in the adhesive of 113 of the example ofFIG. 1D to communicate light therethrough in cooperation with the lightconduit(s) 111 a/112 a in/through layer 105 for communication of lightdata typically involved in pulse oximetry.

The adhesive may thus be placed or disposed on the device 100, in someimplementations substantially permanently, or with some replaceability.In some implementations, the device as shown in FIGS. 1A-1D and/or 1Gwithout (or with in some implementations) the adhesive may be reusable.In many such cases, the adhesive layer 113 may be removed and replacedbefore each subsequent use, though subsequent re-use of and with a layer113 is not foreclosed. In a first or subsequent use with a replaceableadhesive layer 113, it may be that the user applying the device to thepatient, e.g., the physician or technician or even the patient,him/herself, applies the conductive transfer adhesive 113 to the patientside 102 of the device 100. The protective backing 114 may then beremoved, and the device adhered to the patient and activated.

Activation of the device after application to a patient/wearer may occurin a number of ways; in some, it may be pre-set that an affirmativeactivation interaction may not be necessary from the doctor or patientor like due to either an inertial and/or a pulse oximeter activationwhich may be substantially automatically activating, e.g., uponreceiving sufficient minimum input (movement in case of inertial systemor light reflection of blood flow for pulse oximetry); however, a buttonmay be provided at an access 106 or in some other location adjacent theelectronics to allow the patient to start or stop the device orotherwise mark an event if desired. In one exemplar implementation thedevice may be worn for a period such as two weeks for collection of datasubstantially continuously, or at intervals as may be preferred andestablished in or by the systems hereof.

After a monitoring period is over, a physician, technician, patient orother person may then remove the device from the patient body, in someinstances remove the adhesive, in some instances with alcohol, and mayestablish a data communication connection for data transfer, e.g., bywireless communication or by insertion/connection of a USB or like dataconnector to download the data. The data may then be processed and/orinterpreted and in many instances, interpreted immediately if desired. Apower source on board may include a battery and this can then also bere-charged between uses, in some implementations, fully rechargedquickly as within about 24 hours, after which the device could then beconsidered ready for the next patient or next use.

Some alternative conductive adhesives may be used herewith. FIGS. 1E, 1Fand 1G show one such alternative conductive adhesive 113 a; a bottomplan view in FIG. 1E and elevational side views thereof in FIGS. 1F and1G (as being connected to a device 100 in FIG. 1G). In someimplementations, the conductivity may be anisotropic as introducedabove; in some conductive primarily if not entirely in the direction ofthe Z-Axis; perpendicular to the page (into and/or out of the page) inFIG. 1E, and/or vertically or transversally relative to the longhorizontal shown axis of device 100 in the implementation view of FIG.1F.

The implementation of this particular example includes a compositeadhesive 113 a which itself may include some non-conductive portion(s)113 b and some one or more conductive portions 113 c. The adhesivecomposite 113 a may, as described for adhesive 113 above be double sidedsuch that one side adheres to the patient while the other side wouldadhere to the underside 102 of the device 100 (see FIG. 1G) so that oneor more conductive portions 113 c may be disposed or placed inelectrically communicative and/or conductive contact with the integratedelectrodes on the electronic monitoring device 100. Since the electrodeswould operate better where they may be electrically isolated orinsulated from each other, yet each making electrical contact orcommunication with the patient's skin, the adhesive may further be morespecifically disposed in some implementations as follows.

As shown in FIGS. 1E and 1F, three isolated conductive portions 113 cmay be disposed separated from each other by a body portion 113 b whichmay be non-conductive. These could then correspond to the electrodes108, 109, 110 from the above-described examples, and as moreparticularly shown schematically in FIG. 1G (note the scale isexaggerated for the adhesive 113 a and thus, exact matching to theelectrodes of device 100 is not necessarily shown). In some examples,the electrode areas 113 c may be a conductive hydrogel that may or maynot be adhesive, and in some examples, may be made of a conductive anadhesive conductive material such as 3M Corporation 9880 Hydrogeladhesive (3M Company, St. Paul, Minn.). These areas 113 c may then beisolated from each other by a non-conductive material 113 b such as 3MCorporation 9836 tape or 3M double-sided Transfer Adhesive 9917 (3M, St.Paul, Minn.) or equivalent. The additional layer 113 d, if used, mightbe a 3M 9917 adhesive together with the 113 b of a 9836 material. Theseconstructs may provide the effect of creating a low electrical impedancepath in the Z-axis direction (perpendicular to page for FIG. 1E andvertically/transversally for FIGS. 1F and 1G) for the electrode areas113 c, and high electrical impedance path between the electrodes in theX/Y directions. (See FIGS. 1E, 1F and 1G; coplanar with the page in FIG.1E and horizontal and perpendicular to the page in FIGS. 1F and 1G).Thus, a composite adhesive strip can ensure not only device adhering tothe patient, but also that the electrodes whether two or as shown threeelectrodes are conductively connected by conductive portions of theadhesive strip, where the combination of conductive and non-conductiveportions can then reduce signal noise and/or enhance noise freecharacteristics. Electrodes that move relative to skin can introducenoise; that is, electrodes electrically communicative/connected to theskin via a gel may move relative to the skin and thus introduce noise.However, with one or more conductive adhesive portions in a compositeadhesive connected to respective electrodes and then substantiallysecurely connected to the skin will keep the respective electrodessubstantially fixed relative to the skin and thereby reduce or eveneliminate electrode movement relative to the skin. Removal of suchmovement would then remove noise which would thereby provide a cleansignal that can allow for monitoring cardiac P waves which enhances thepossibility to detect arrhythmias that couldn't otherwise be detected.Further description is set forth below.

In some implementations, a further optional connective and/or insulativestructure 113 d may be implemented as shown in FIGS. 1F and/or 1G, toprovide further structural and insulative separation between electrodeswith connected to a device 100 on the underside 102 thereof (see FIG.1G). Though shown separate in FIGS. 1F and 1G, it may be contiguous withthe insulative adhesive 113 b of these views.

Further alternatives related to the adhesive may be used. In someimplementations, a composite adhesive strip may be used havingproperties to reduce one or more motion artifacts. Typical ECGattachment systems use a conductive gel located over the electrode.Here, however, a hydrogel adhesive may be used which is embedded in acontinuous sheet of laminated adhesives that cover the selected regionsor the entire footprint of the device. The fact that the hydrogel itselfhas strong adhesive properties coupled with the complete coverage of thedevice with adhesives may assure a strong bond between the device andthe patient's skin. Contributing to motion artifact reduction may be analternative vertical placement of the device on the sternum whichresults in reduced motion artifacts for one or more of ECG signals,photoplethysmography waveforms, and oxygen saturation signals.

In some implementations, composite adhesive improvements may includewater-proof encapsulation of the hydrogel adhesive to prevent ohmicimpedance reduction resulting in reduction of signal amplitude. This mayalso help prevent hydrocolloid adhesive degradation. In particular, asshown the non-limitative alternative exemplar in FIGS. 1I and 1J;several layers may be used. Herein, Layer 1 may be a hydrocolloid thatis an adhesive designed for long term skin contact by absorbing sweatand cells. Layer 2 may then also be a layer designed for long-term skincontact, however, this layer 2 isolates Layer 3 from contacting theskin. The smaller dimensions of Layer 2 create a gap between Layers 1and 3. When Layer 1 and 3 bond together, it forms a water-tight sealaround Layer 2. This layer, Layer 2, also isolates the Hydrocolloid fromthe Hydrogel Adhesive, protecting the adhesive properties of theHydrocolloid. Layers 3 and 5 would then generally be waterproof layersthat are electrically isolating, double-sided adhesives. These twolayers encapsulate the hydrogel adhesive, preventing a “short circuit”described relative to layer 4 below. Layer 4 is the hydrogel adhesivethat is the conductive element hereof. The three islands of hydrogeladhesive of Layer 4 must be kept electrically isolated from each other.However as the hydrocolloid in layer 1 absorbs sweat, it too becomesconductive and creates a potential “short circuit” between the threeislands of hydrogel adhesive in Layer 4, reducing signal amplitude.Nevertheless, this “short circuit” may be prevented by layers 3 and 5,described above.

In some one or more additional alternative implementations, temperaturemay be a parameter determined hereby. This may be by a single sensor orplural sensors as described herein. In some temperature implementations,infant or neonate temperature may be sought data for capture hereby, ortemperature may be used with other users, adult or otherwise.

Infant and/or neonate temperature sensing can be of significantassistance in health monitoring. Forehead or other use may be one suchapplication. Another set of possible applications may include methodsand apparatuses for sensing the temperature of both an infant and amother engaged in so-called “Kangaroo Care”. There is evidence thatpre-mature infants may benefit more from constant contact with aparent's or the mother's skin than from being placed in an incubator.There is also evidence of lower mortality rates.

An apparatus 100 a for dual temperature sensing, the infant wearer 1000and the mother 1010 or ambient air 1011, is shown in the accompanyingfigure, FIG. 1R. The substrate 1105 is preferably a small, flexiblecircuit board, in some examples, approximately twenty (20) mm×thirty(30) mm. The board 1105 may be disposed to contain circuitry 1103 for,for example, sensing relative X-Y-Z position and/or acceleration, and/orBluetooth or other wireless data/signal connectivity, as well as, inmany examples, a replaceable and/or rechargeable battery for extendeduse, as for example, seven (7) days of continuous monitoring (circuitelement alternatives not all separately shown in FIG. 1R). The apparatus100 a may be held to the infant with an adhesive, such as the compositeadhesive 1113 shown in FIG. 1R, which may further be, for example, adisposable, medical grade, double-sided adhesive.

Each of two temperature sensors 1111 a and 1111 b may be disposed onalternative opposing sides 1101, 1102 of the apparatus 100 a, and may bethermally isolated from each other, as well as often being waterproof,water tight or water resistant. A thermally insulating or isolationlayer 1103 a may provide the thermal isolation of the electronics 1103and/or sensors 1111 a and 1111 b. A further spacer 1103 b may bedisposed through the insulating/isolating layer 1103 a to provide athroughway for electronic communication of the sensor 1111 b to theelectronics layer 1103. A silicone bead 1104 may be provided forisolating and assisting in giving a waterproof or water-resistant sealon the “infant side” 1102, and a silicone cover 1121 may provide awaterproof or waterproof barrier on the “mother side” 1101. The sensor1111 b on the “mother side” or top or exterior side 1101 may be slightlyprotruding relative to the cover 1121 with in many implementations athin/thinner layer of covering material and/or silicone thereover. Thesensor 1111 a on the child side or patient or circuit side 1102 may beprotruding past, or through the adhesive and/or disposed exposed oralso/alternatively covered with a thin protectant layer for waterproofness, or tightness or resistance.

The thermally insulating layer may provide one or two or more functions.It may provide for or allow the “infant side” sensor 1111 a to reachequilibrium, thus providing an accurate “core temperature” of theinfant. It may also or alternatively isolate the infant's temperaturereading from the mother's or ambient. The “mother side” sensor 1111 bdoes not have to provide an accurate core temperature for the mother.Typically, the function of sensor 1111 b would be to differentiatewhether or not the infant is in the correct direct contact with themother's skin; i.e., to provide a relative measurement for determiningwhether the infant is in relative contact or not in relative contactwith the mother. If the infant is facing the wrong way, but is still inthe “pouch” the sensor will read that environment's ambient temperature.If the infant is out of the pouch, it will read the room ambienttemperature. The relative differences would be interpretable to providean indication of what position the infant is in; whether in contact, orin close association in a controlled “pouch” environment (but not incontact), or outside the pouch in a further removed environment.

An alarm from a Bluetooth or otherwise wirelessly connected device maybe used to alert the mother (or health care professional) that theinfant is no longer in the correct desired position, or no longer in the“pouch”.

Some alternative implementations hereof may include a driven right legECG circuit with one or more chest only electrodes (“Driven ChestElectrode”). In addition to the electrodes used to measure a single ormultiple lead electrocardiogram signal, a device 100 may use anadditional electrode, as for example the reference electrode 110 (seeFIGS. 1A, 1C, 1D and 1G, e.g.) to reduce common mode noise. Such anelectrode may function in a manner similar to the commonly-used drivenright leg electrode, but may here be located on the patient's chestrather than on the patient's right leg but nevertheless thisthird/reference electrode may play the role of the leg electrode. Thischest electrode may thus mimic a right leg electrode and/or beconsidered a proxy driven right leg electrode. A circuit, or portion ofan overall circuit, adapted to operate in this fashion may include anumber of amplifier stages to provide gain, as well as filtering toensure circuit stability and to shape the overall frequency response.Such a circuit may be biased to control the common mode bias of theelectrocardiogram signal. This driven chest electrode implementation maybe used in conjunction with a differential or instrumentation amplifierto reduce common mode noise. In this case, the sense electrode may beused as one of the electrocardiogram electrodes. Alternatively, asingle-ended electrocardiogram amplifier may be used where thedifferential electrocardiogram signal is referenced to ground or to someother known voltage.

A circuit or sub-circuit 200 using a transistor 201 as shown in FIG. 2may be such a circuit (aka module) and may thus include as further shownin FIG. 2A, a sense electrode 202, a drive electrode 203, and anamplifier 204. Both the sense and drive electrodes 202, 203 are placedon the patient's chest such that they provide an electrical connectionto the patient. The amplifier 204 may include gain and filtering. Theamplifier output is connected to the drive electrode, the invertinginput to the sense electrode, and the non-inverting input to a biasvoltage 205. The amplifier maintains the voltage of the sense electrodeat a level close to the bias voltage. An electrocardiogram signal maythen be measured using additional electrodes. Indeed, as was the casefor the improved conductivity through use of anisotropic adhesiveportions above, here also or alternatively, the use of this thirdelectrode as a proxy for a right leg electrode (i.e., proxy driven rightleg electrode) can provide signal reception otherwise unavailable. Cleansignals may thus allow for receiving cardiac P waves which enhances thepossibility to detect arrhythmias that couldn't otherwise be detected.

Further alternative descriptions of circuitry include that which isshown in FIGS. 2B and 2C; in which are shown non-limiting alternativesin which three adjacent electrodes E1, E2, and E3 may be used to pick upthe ECG signal, one of which electrodes playing the role of the distantlimb electrode of traditional ECG monitors. Because theelectrode-patient interface has an associated impedance (Re1 and Re2),current flowing through this interface will cause a difference involtage between the patient and the electrode. The circuit may use asense electrode (E1) to detect the patient voltage. Because thisexemplar circuit node has a high impedance to circuit ground (GND), verylittle current flows through the electrode interface, so that thevoltage drop between the patient and this node is minimized. The firstof these alternative, non-limiting circuits (FIG. 2B) also contains anamplifier (U1) whose low-impedance output is connected to a separatedrive electrode (E2). The amplifier uses negative feedback to controlthe drive electrode such that the patient voltage (as measured by thesense electrode E1) is equal to the bias voltage (V1). This mayeffectively maintain the patient voltage equal to the bias voltagedespite any voltage difference between the driven electrode (E2) and thepatient. This can include voltage differences caused by powerline-induced current flowing between the drive electrode and the patient(through Re2). This arrangement differs from a traditional‘driven-right-leg’ circuit in at least two ways: the driven electrode isplaced on the patient's chest (rather than the right leg), and the ECGsignal is a single-ended (not differential) measurement taken from athird electrode (E3). Because all electrodes are located on thepatient's chest in a chest-mounted example, a small device placed theremay contain all the necessary electrodes for ECG measurement. Onepossible benefit of the single-ended measurement is that gain andfiltering circuitry (U2 and associated components (FIG. 2C)) necessaryto condition the ECG signal prior to recording (ECG Output) requiresfewer components and may be less sensitive to component tolerancematching. The examples of FIGS. 2A, 2B and 2C are non-limiting examplesand not intended to limit the scope of the claims hereto as othercircuits with other circuit elements can be formed by skilled artisansin view hereof and yet remain within the spirit and scope of claimshereof.

In many implementations, a system hereof may include other circuitryoperative together with the ECG electrodes, which may thus beaccompanied by other sensors to provide time concordant traces of: i)ECG p-, qrs-, and t-waves; ii) O2 Saturation, as measured by PulseOxymetry; and/or iii) xyz acceleration, to provide an index of physicalactivity. Such circuitry may be implemented to one or more of thefollowing electrical specifications. The overall system might in someimplementations include as much as two weeks (or more) of continuous runtime; gathering data during such time. Some implementations may beadapted to provide as many or even greater than 1000 uses. Alternativesmay include operability even after or during exposure to fluids orwetness; in some such examples being water resistant, or waterproof, orwatertight, in some cases continuing to be fully operable when fullysubmerged (in low saline water). Other implementations may include fastdata transfer, as for an example where using an HS USB for full datatransfer in less than about 90 seconds. A rechargeable battery maytypically be used.

A further alternative implementation may include an electronic “ground”:In a device hereof, mounted entirely on a flexible circuit board, theground plane function may be provided by coaxial ground leads adjacentto the signal leads. The main contribution of this type of groundingsystem may be that it may allow the device the flexibility required toconform and adhere to the skin.

For electrocardiograph; EKG or ECG, some implementations may includegreater than about 10 Meg Ohms input impedance; some implementations mayoperate with a 0.1-48 Hz bandwidth; and some with an approximate 256 HzSampling Rate; and may be implementing 12 Bit Resolution. For PPG andPulse Oximeter, operation may be with 660 and 940 nm Wavelength; about80-100 SpO2 Range; a 0.05-4.8 Hz Bandwidth; a 16 Hz Sampling Rate; and12 bit resolution. For an accelerometer: a 3-Axis Measurement may beemployed, and in some implementations using a ±2 G Range; with a 16 HzSampling Rate; and a 12 Bit Resolution.

For pulse oximetry, an option for PPG ambient light subtraction may beincluded. A method and circuitry for reducing errors in pulse oximetrycaused by ambient light is described and a circuitry option shown inFIG. 2D. Here a correlated double sampling technique is shown for use toremove the effect of ambient light, photo-detector dark current, andflicker noise.

The schematic shown in FIG. 2D may be used where, first, the noisesignal may be measured. The light sources are turned off, switch S1 isclosed, and switch S2 is open. This allows charge proportional to thenoise signal to accumulate on C1. Then switch S1 is opened. At thispoint the voltage on C1 is equal to the noise signal voltage. Next, thelight signal may be measured. The light source is turned on, switch S2is closed, and charge is allowed to flow through C1 and C2 in series.Then, S2 is opened, and the voltage is held on C2 until the nextmeasurement cycle when the whole process is repeated.

If C1 is much larger than C2, nearly all the voltage will appear on C2,and the voltage on C2 will be equal to the noise-free signal (s).Otherwise, the voltage on C2 will be a linear combination of theprevious C2 voltage (p) and the noise-free signal: (C2*s+C1*p)/(C1+C2).This has the effect of applying a first-order, low-pass, IIRdiscrete-time filter to the signal. If this filtering effect is notdesired, the voltage on C2 may be discharged to zero before the signalis measured each cycle, so that the signal held on C2 is simply:(C2*s)/(C1+C2).

This circuit may be used with a trans-impedance amplifier in place ofresistor R, a phototransistor in place of the photodiode, and FETs inplace of the switches. The output may be followed by additionalbuffering, amplification, filtering and processing stages.

Some summary methodologies may now be understood with relation to FIG.3, though others may be understood through and as parts of the remainderof the disclosure hereof. A flow chart 300 as in FIG. 3 may demonstratesome of the alternatives; where an initial maneuver 301 might be theapplication of the device 100 to the patient. Indeed, this might includesome one or more of the alternatives for adhesive application asdescribed here above, whether by/through use of an adhesive such as that113 of FIG. 1D, or that of FIGS. 1E, 1F and/or 1G. Then, as shown, inmoving by flow line 311, a data collection operation 302 may beimplemented. Note, this might include a continuous or substantiallycontinuous collection or an interval or periodic collection or perhapseven a one-time event collection. This may depend upon the type of datato be collected and/or be dependent upon other features or alternatives,as for example whether a long term quantity of data is desired, for ECGfor example, or whether for example a relative single data point mightbe useful, as in some cases of pulse oximetry (sometimes a singlesaturation point might be of interest, as for example, if clearly toolow, though comparison data showing trending over time, may indeed bemore typical).

Several alternatives then present in FIG. 3, flow chart 300; a firstsuch might be the following of flowline 312 to the transmission of dataoperation 303, which could then involve either wireless or wired (e.g.,USB or other) data communication from the device 100 to data analysisand/or storage devices and/or systems (not separately shown in FIG. 3;could include computing devices, see e.g., FIG. 4 described below, orthe like). Options from this point also appear; however, a first suchmight include following flow line 313 to the data analysis operation 304for analyzing the data for determination of the relative health and/orfor condition diagnosis of a patient. Computing systems, e.g., acomputer (could be of many types, whether hand-held, personal ormainframe or other; see FIG. 4 and description below) could be used forthis analysis; however, it could be that sufficient intelligence mightbe incorporated within the electronics 103 of device 100 such that someanalysis might be operable on or within device 100 itself. Anon-limiting example, might be a threshold comparison, as for examplerelative to pulse oximetry where when a low (or in some examples,perhaps a high) threshold level is reached an indicator or alarm mightbe activated all on/by the electronics 103 of the device 100.

A similar such example, might be considered by the optional alternativeflow path 312 a which itself branches into parts 312 b and 312 c.Following flow path 312 a, and then, in a first example path 312 b, askip of the transmit data operation 303 can be understood wherebyanalysis 304 might be achieved without substantial data transfer. Thiscould explain on board analysis, whether as for example according to thethreshold example above, or might in some instances include moredetailed analysis depending upon how much intelligence is incorporatedon/in the electronics 103. Another view is relative to how muchtransmission may be involved even if the transmission operation 303 isused; inasmuch as this could include at one level the transmission ofdata from the patient skin through the conductors 108, 109 and/or 110through the traces 107 to the electronics 103 for analysis there. Inother examples, of course, the transmission may include off-boarddownloading to other computing resources (e.g., FIG. 4). In some cases,such off-loading of the data may allow or provide for more sophisticatedanalysis using higher computing power resources.

Further alternatives primarily may involve data storage, both when andwhere, if used. As with intelligence, it may be that either some or nostorage or memory may be made available in/by the electronics 103on-board device 100. If some storage, whether a little or a lot, is madeavailable on device 100, then, flow path 312 a to and through path 312 cmay be used to achieve some storing of data 305. This may in many casesthen, though not necessarily be before transmission or analysis (note,for some types of data multiple paths may be taken simultaneously, inparallel though perhaps not at the same time or serially (e.g., paths312 b and 312 c need not be taken totally to the exclusion of theother), so that storage and transmission or storage and analysis mayoccur without necessarily requiring a completion of any particularoperation before beginning or otherwise implementing another). Thus,after (or during) storage 305, flow path 315 a may be followed forstored data which may then be transmitted, by path 315 b to operation303, and/or analyzed, by path 315 c to operation 304. In such a storageexample, which in many cases may also be an on-board storage example,data can be collected then stored in local memory and lateroff-loaded/transmitted to one or more robust computing resources (e.g.,FIG. 4) for analysis. Frequently, this can include long term datacollection, e.g., in the manner of days or weeks or even longer, and maythus include remote collection when a patient is away from a doctor'soffice or other medical facilities. Thus, data can be collected from thepatient in the patient's real world circumstances. Then, aftercollection, the data can be transmitted from its storage on device 100back to the desired computing resource (FIG. 4, e.g.), and suchtransmission might be wireless or wired or come combination of both, asfor example a blue tooth or Wi-Fi connection to a personal computer(FIG. 4 for one example) which might then communicate the data over theinternet to the designated computer for final analysis. Another examplemight include a USB connection to a computer, either to a PC or amainframe (FIG. 4), and may be to the patient computer or to the doctorcomputer for analysis.

If little or no storage or memory is resident on device 100 (or in someexamples even where there may be a large amount of resident memoryavailable), then, relatively soon after collection, the data would needto or otherwise might desirably either or both be transmitted and thenstored, see path 313 a after operation 303, and/or transmitted andanalyzed, paths 312 and 313. If path 313 a is used, then, moretypically, the data storage may be in/on computing resources (not shownin FIG. 3, but see FIG. 4 described below) off-board (though on-boardmemory could be used as well), and then, any of paths 315 a, 315 b and315 c may be used.

A feature hereof may include an overall system including one or moredevices 100 and computing resources (see FIG. 4, for example) whetheron-board device(s) 100, or separate, as for example in personal ormobile or hand-held computing devices (generally by FIG. 4), the overallsystem then providing the ability for the physician or doctor to haveimmediate, in-office analysis and presentation of collected test data.This would in some implementations allow for on-site data analysis fromthe device without utilization of a third party for data extraction andanalysis.

Alternative implementations hereof may thus include one or more hardwareand software combinations for multiple alternative data sourceinterpretations. As noted above, a device 100 hereof includes hardwarethat monitors one or more of various physiologic parameters, thengenerates and stores the associated data representative of the monitoredparameters. Then, a system which includes hardware such as device 100and/or the parts thereof, and software and computing resources (FIG. 4,generally) for the processing thereof. The system then includes not onlythe collection of data but also interpretation and correlation of thedata.

For example, an electrocardiogram trace that reveals a ventriculararrhythmia during intense exercise may be interpreted differently thanthe same arrhythmia during a period of rest. Blood oxygen saturationlevels that vary greatly with movement can indicate conditions that maybe more serious than when at rest, inter alia. Many more combinations ofthe four physiologic parameters are possible, and the ability ofsoftware hereof to display and highlight possible problems will greatlyaid the physician in diagnosis. Thus, a system as described hereof canprovide beneficial data interpretation.

Some of the features which can assist toward this end may be subsumedwithin one or more of operations 303 and 304 of FIG. 3, wherein datacollected on a device 100 can rather simply be communicated/transmittedto computing resources (again, whether on-board device 100 or discretetherefrom as e.g., FIG. 4). For an example, when a patient having had adevice applied (operation 301) may return to a physician's office aftera test period wherein data was collected (operation 302) the device isconnected via one or more data transmission alternatives, as forexample, USB to a computer (Windows or Mac) (generally with reference toFIG. 4 and description thereof) in the office, allowing immediateanalysis by the physician while the patient waits (note, the device 100may first have been removed from the patient or might remain thereonpending transmission and analysis for determination of whether more datamay be desired). In some implementations, data analysis time may berelatively quick, at approximately 15 minutes in some implementations,and might be achieved with a user-friendly GUI (Graphic User Interface)to guide the physician through the analysis software.

The analysis/software package may be disposed to present the physicianwith results in a variety of formats. In some implementations, anoverview of the test results may be presented, either together with orin lieu of more detailed results. In either case, a summary of detectedanomalies and/or patient-triggered events may be provided, either aspart of an overview and/or as part of the more detailed presentation.Selecting individual anomalies or patient-triggered events may providedesirable flexibility to allow a physician to view additional detail,including raw data from the ECG and/or from other sensors. The packagemay also allow data to be printed and saved with annotations inindustry-standard EHR formats.

In one implementation, patient data may be analyzed with software havingthe one or more of the following specifications. Some alternativecapabilities may include: 1.Data Acquisition; i.e., loading of datafiles from device; 2. Data Formatting; i.e., formatting raw data toindustry standard file formats (whether, e.g., aECG (xml); DICOM; orSCP-ECG) (note, such data formatting may be a part of Acquisition,Storage or Analysis, or may have translation from one to another (e.g.,data might be better stored in a compact format that may needtranslation or other un-packing to analyze)); 3. Data Storage (whetherlocal, at a clinic/medical facility level or e.g., in the Cloud(optional and allows offline portable browser basedpresentation/analysis); 4. Analysis which inter alia, may include, e.g.,noise filtering (High pass/Low pass digital filtering); and/or QRS(Beat) detection (in some cases, may include Continuous Wave Transform(CWT) for speed and accuracy); and/or 5. Data/Results Presentation,whether including one or more graphical user interface(s) (GUIs) perhapsmore particularly with an overall Summary and/or General Statisticsand/or Anomaly Summary of Patient triggered event(s); presentation ofadditional levels of detail whether of Strip view(s) of anomaly data byincident (previous, next) Blood Oxygen saturation, stress correlation orthe like; and/or allowing care provider bookmarking/annotations/notes byincident and/or Print capability.

Further, on alternative combinations of hardware with proprietarysoftware packages: I) One on-device software package may be adapted tostore the measurements from the data signals acquired from one or moreof EKG/ECG (whether right leg and/or p-, qrs- and/or t-waves), or O2saturation, or xyz acceleration, in a time concordant manner, so that aphysician may access a temporal history of the measurements (say, insome examples, over a 1-2 week interval), which would provide usefulinformation on what the patient's activity level was prior to, during,and after the occurrence of a cardiac event. ii) an alternative toalternately manage the real-time transmission of the real-time measuredparameters to a nearby station or relay. And/or; iii) an off-device ECGanalysis software aimed at recognizing arrhythmias.

The software mentioned above may be industry understood softwareprovided by a 3rd party, or specially adapted for the data developed andtransmitted by and/or received from a wearable device 100 hereof.Thorough testing using standard (MIT-BIH/AHA/NST) arrhythmia databases,FDA 510(k) approvals preferred. Such software may be adapted to allowone or more of automated ECG analysis and interpretation by providingcallable functions for ECG signal processing, QRS detection andmeasurement, QRS feature extraction, classification of normal andventricular ectopic beats, heart rate measurement, measurement of PR andQT intervals, and rhythm interpretation.

In many implementations, the software may be adapted to provide and/ormay be made capable of supplying one or more of the followingmeasurements:

TABLE 1 1. Heart Rate Min, Max and Average 2. QRS duration average 3. PRinterval average 4. QT interval average 5. ST deviation averageand, may be adapted to recognize a broad range of arrhythmias such asthose set forth here:

TABLE 2A 1. SINUS RHYTHM 2. SINUS RHYTHM + IVCD 3. SINUS BRADYCARDIA 4.SINUS BRADYCARDIA + IVCD 5. SINUS TACHYCARDIA 6. PAUSE 7. UNCLASSIFIEDRHYTHM 8. ARTIFACT

This first group of 8 given above are arrhythmia types that may berecognizable even if there is no discernible P wave. They are the onestypically recognized by existing products in the outpatient monitoringmarket that we propose to address.

A second set or group of arrhythmias; below, may require a discernibleand measurable P wave. Some implementations hereof may be adapted to beable to detect and recognize them, as device 100 may be able asdescribed above to detect P waves, depending of course, and for example,on whether the strength of the P wave which may be affected by device100 placement or patient physiology.

TABLE 2B 9. ATRIAL FIBRILLATION/FLUTTER SVR (slow) 10. ATRIALFIBRILLATION/FLUTTER CVR (normal rate) 11. ATRIAL FIBRILLATION/FLUTTERRVR (rapid 12. FIRST DEGREE AV BLOCK + SINUS RHYTHM 13. FIRST DEGREE AVBLOCK + SINUS TACHYCARDIA 14. FIRST DEGREE AV BLOCK + SINUS BRADYCARDIA15. SECOND DEGREE AV BLOCK 16. THIRD DEGREE AV BLOCK 17. PREMATUREATRIAL CONTRACTION 18. SUPRAVENTRICULAR TACHYCARDIA 19. PREMATUREVENTRICULAR CONTRACTION 20. VENTRICULAR COUPLET 21. VENTRICULAR BIGEMINY22. VENTRICULAR TRIGEMINY 23. IDIOVENTRICULAR RHYTHM 24. VENTRICULARTACHYCARDIA 25. SLOW VENTRICULAR TACHYCARDIA

Further in alternative software implementations; some sample screenshotsare shown in FIG. 5. A first such alternative is shown in FIG. 5A, whichis an example screenshot showing ECG and Oxygen Saturation data taken byusing a patch device such as a device 100 hereof. An extremely cleansignal is shown (no filtering or smoothing has been done on this data).Distinct p-waves are also shown (3 of which are shown as an example witharrows). P wave detection can be extremely important for ECG anomalydetection. Oxygen Saturation, as measured by Pulse Oxymetry, is shown onthe bottom plot. This is data taken by a device on the chest, and istaken in time concordance with the ECG data.

Another alternative is shown in FIG. 5B, which is an example screenshotof Analysis Software. This is a sample of ECG data taken from theMIT-BIH Arrhythmia Database, Record 205. As analyzed by the Analysissystem hereof, we see in the Event Occurrences Summary list (top, left)five (5) anomaly types (plus normal sinus rhythm). This list also showsthe number of occurrences of each anomaly, total duration of the anomalyin the complete ECG, and the percent time this anomaly occurs in thecomplete ECG. To view specific instances of each anomaly, the userdouble clicks the specific row in the Event Occurrences Summary list, asshown in FIG. 5C.

As introduced, FIG. 5C is an example screenshot showing specificinstance of Ventricular Tachycardia. The ECG plot automaticallynavigates to the specific time in the ECG waveform, and marks thebeginning and end of the event. More detailed data about this specificevent is now shown in the Occurrence Details: HR Average, HR Max, etc.for the duration of this event. To show the instances of another anomalyin this ECT, the user can click on the Premature Ventricular Contraction(PVC) row of the Event Occurrences Summary, as shown FIG. 5D.

As introduced, FIG. 5D is an example screenshot showing specificinstance of Premature Ventricular Contraction. This shows occurrences ofthe PVC. The Start Times list (middle top) shows all instances of PVCoccurrences in this ECG, and lists the start time for each occurrence.In this case, the user can click on the PVC that starts at 00:15:27 (the11^(th) occurrence). The ECG plot is automatically taken to this pointin time to show and indicate the PVC instances in the waveform. Sincethere are 3 instances of a PVC in this timeslot, all 3 occurrences aremarked.

As mentioned above, in one aspect of the developments hereof, ECGsignals collected in time concordance with pulse oximetry signals may beused to reduce the noise in the pulse oximetry signals and to permit thecalculation of values for oxygen saturation, particularly incircumstances where sensors pulse oximetry data are placed onnoise-prone locations of a patient, such as the chest. In someembodiments, this aspect may be implemented by the following steps: (a)measuring an electrocardiogram signal over multiple heart beats; (b)measuring one or more pulse oximetry signals over multiple heart beatssuch that the electrocardiogram signal and the one or more pulseoximetry signals are in time concordance over one or more heart beats;(c) comparing a portion of the electrocardiogram signal and the one ormore pulse oximetry signals in time concordance over one or more heartbeats to determine a constant component and a primary periodic componentof each of the one or more pulse oximetry signals; and (d) determiningoxygen saturation from the constant components and primary periodiccomponents of the one or more pulse oximetry signals. Measurement of theECG signals and pulse oximetry signals may be implemented by embodimentsof devices hereof. In particular, pulse oximetry signals may be areflective infrared signal and a reflective red light signal collectedby a photodetector in a device hereof Alternatives may include othercolors, as for example green in addition to or in lieu of one or both ofred and infrared. Such alternatives are described further below.

Intervals of pulse oximetry signals corresponding to heart beats may bedetermined by comparing such signals to the time concordant ECG signals.For example (not intended to be limiting), successive R-wave peaks of atime concordant ECG signal may be used to identify such intervals,although other features of the ECG signal may be used as well. Once suchintervals are identified, values at corresponding times within theintervals may be averaged to reduce signal noise and to obtain morereliable values for the constant components (sometimes referred to asthe “DC components”) and the main periodic components (sometimesreferred to as the “AC components”) of the pulse oximetry signals, e.g.Warner et al, Anesthesiology, 108: 950-958 (2008). The number of signalvalues recorded in an interval depends on the signal sampling rate ofthe detectors and processing electronics employed. Also, as theintervals may vary in duration, the averaging may be applied to a subsetof values in the intervals. As described below, oxygen saturation valuesmay be computed from such DC and AC components using conventionalalgorithms. The number of heart beats or intervals over which suchaverages may be computed may vary widely, as noted below. In someembodiments, signals from one or more heart beats or intervals may beanalyzed; in other embodiments, signals from a plurality of heart beatsor intervals may be analyzed; and in some embodiments, such pluralitymay be in the range of from 2 to 25, or in the range of from 5 to 20, orin the range of from 10 to 20.

As described, a method of pulse oximetry measures photoplethysmogramsignals at red and infrared wavelengths. The DC or mean value isestimated and subtracted, and the ratio of AC or pulsatile signal isestimated and/or averaged. Linear regression between the two signals canbe used as described below. However, performance is limited becausesimilar noise exists in both the red and infrared signals.Photoplethysmography taken using green light (˜550 nm) is more resilientto motion noise because the light is absorbed much more by blood than bywater or other tissue. However, the difference between oxygenated anddeoxygenated blood in the green region of the spectrum is much less thanred. In an alternative, a green PPG signal (or long time average ofred/IR (see below)) may be used to determine the shape of the pulsatilesignal. A weighted average of any number of different wavelengths (suchas green, red and infrared) may be used to estimate the shape of thepulsatile waveform.

In further alternative implementations, a linear regression algorithmfor Oxygen Saturation may be used. As such, either or both the patient'sECG signal and/or a green (or other color) LED PPG signal may be used.For a first example, an ECG signal may be used to determine when heartbeats occur. The beat locations allow correlated time averaging of eachof the two photoplethysmogram signals. A linear regression of theensemble averages may then be used to determine the linear gain factorbetween the two signals. This gain factor can be used to determine thepatient oxygen saturation.

If/when in the alternative and/or in addition, photoplethysmography(PPG) using green light (˜550 nm) is implemented, the PPG signal may beused determine the shape of the pulsatile signal. This lower-noisesignal may then be used as the independent variable for linearregression with both the red and infrared signals. The ratio of thesetwo regression results is an estimate of the correlation between the redand infrared signals. Noise can be reduced by ensemble averaging overmultiple heart beats as disclosed herein (see e.g., description offrames below). In addition to or instead of using an ECG signal todetermine beat timing, the green wavelength PPG signal may be used.Alternatively, a weighted average of any number of different wavelengths(such as green, red and infrared or long time average of red/IR (seebelow)) may be used. The ensemble averaging may be improved by detectingand removing outlier beats, possibly by discarding beats that have lesscorrelation to the estimated ensemble average than others, or byestimating noise and weighting beats from areas of high noise less.Noise can also be improved through longer averaging periods.

As such, included may be a method for health monitoring comprising:determining from either or both a user's ECG and/or a firstphotoplethysmogram PPG signal and/or a weighted combination ofwavelengths when heart beats occur; time averaging the firstphotoplethymogram PPG signal to generate a first pulse shape template ordataset; time averaging each of two additional photoplethysmogramsignals correlated to the beat locations; one of the additional signalsbeing red, the other additional signal being IR; generating ensembleaverages for each of the red and IR signals; comparing each of the redand IR ensemble averages to the first pulse shape template or dataset;using a linear regression of each of the red and IR ensembleaverage-comparisons to the first pulse template or dataset to determinethe linear gain factor between the two signals; determining from thegain factor the patient oxygen saturation.

In a similar view; included may be a method for determining pulseoxygenation; comprising: a) detecting heart beats; using ECG, usinggreen, or using a weighted combination of wavelengths; b) generating oneor more of a first pulse shape template or a dataset representing afirst pulse shape, including using green wavelengths, an ensembleaverage of green over approximately the same amount of time as foreither red or IR, an ensemble average of multiple wavelengths overapproximately the same amount of time as for either red or IR, or anensemble average of multiple wavelengths over significantly longer thanthe amount of time as for either red or IR; can use ensemble averagegives beat shape; or a long time average of a single wavelength of anycolor; c) obtaining a red pulse shape template or dataset representingsame and an IR pulse shape template or dataset representing same, andcompare each of these to the first pulse shape above; and, d)correlating via linear regression between red ensemble average with thefirst pulse shape template or dataset to the IR ensemble average withthe first pulse shape or dataset, where the ratio of these correlationsis then used as the AC ratio for oxygen saturation.

The pulse shape template or dataset is in some implementations similarto the reference frame template described herein as well in that thepulse shape template represents a long-term ensemble average of the PPGsignal. However, a difference is that the reference frame templatedescribed herein elsewhere was there designated for pulse transit time,while in the present description related to a first pulse shape ordataset or the like, is for oxygen saturation.

While a first method may be one where green light is used for the beatdetection, other methods will be viable as well, as where ECG is usedfor beat detection. Further, the alternatives include green or a longred and IR average used for the first pulse shape, and a shorter red andIR is used for the oxygen saturation comparisons to the first pulseshape. It may be helpful to understand that a long red and IR averageused for the first pulse waveform shape (or dataset) is in relation tothe relatively shorter red/ir signals used for the oxygen saturationmeasurement. Because the shape is expected to change slower than theoxygen saturation, a long average can be used for the shape, while stillusing a shorter average (and thus getting faster response times) for theoxygen saturation part.

Note, green has been found desirable because it has a high signal tonoise ratio; the pulse signal is strong relative to other possiblemotion noise. However, other wavelengths could be used instead of green,i.e. green could be replaced by other colors in the spectrum of light,keeping in mind, some colors will behave better or other colors worse inthe relationship of signal to noise. Note, other colors, even without adesirable signal to noise ratio can be used herein or herewith.Similarly, the preference for red and/or IR wavelengths has been that ithas been found that red and/or IR have provided good relativereflectivity to the particular oxygenation of hemoglobin blood in a testsubject. Each of oxygenated blood reflects an effective amountcomparatively of red light and de-doxygenated blood reflects aneffective amount comparatively of infrared, IR, light. Other colors canbe used instead of red and IR throughout, though the other colors mayhave less (or more) effectiveness in particular applications. It shouldalso be noted that as understood in the art, whenever any particularcolor of light is described, a number of discrete wavelengths may beunderstood as falling within such definition, and that utility may fallwithin or outside the definition, though preferences may be identifiedby general color. Thus colors other than green or red or IR areunderstood to be used and/or such color selection may be limited only byminimal effectiveness in either signal to noise ratio and/orreflectiveness related to oxygenation or other utility.

ECG or green PPG (or like) or long time average of red/IR (see below)data may be recorded in time-concordance with two or morephotoplethysmographs of different light wavelengths. The heart beats aredetected in the ECG or green PPG signal. These heart beats allow fordefinition of a ‘frame’ of photoplethysmogram data for the time betweentwo adjacent heart beats. Two or more of these frames can then beaveraged together at each point in time to create an average frame forthe time interval. Because the photoplethysmogram is correlated with theheartbeat, the photoplethysmograph signal is reinforced by thisaveraging. However, any motion artifact or other noise source that isuncorrelated in time with the heartbeat is diminished. Thus, thesignal-to-noise ratio of the average frame is typically higher than thatof the individual frames.

Having constructed an average frame for at least twophotoplethysmographs of different light wavelengths, linear regressioncan then be used to estimate the gain between the two average framesignals. This gain value may be used to estimate blood oxygen saturationinformation or other components present in the blood such as hemoglobin,carbon dioxide or others. The process may be repeated for additionaland/or alternative light wavelengths in order to do so.

Exemplar/alternative methods hereof may include determining the gainbetween particular signals, as between the red and IR and/or green framesignals, if/when such may be used. These may be found by averaging thetwo frames together first. This may result in a signal with reducednoise. The gain is found by performing linear regression of the redversus combined and IR versus combined and then finding the ratio ofthese two results; or linear regression of the red versus combined withgreen and IR versus combined with green and then finding the ratio ofthese two results; or linear regression of red versus green and IRversus green and then finding the ratio of these two results; or bylinear regression of combining green with each of red and IR and usingthe ratio of these results.

Another method involves selecting a possible gain value, multiplying theaverage frame signal by it, and determining the residual error withrespect to an average frame of a different wavelength. This process maybe repeated for a number of potential gain values. While simple linearregression finds the global minimum gain value, this method allows forfinding local minima. Thus, if it is likely that the global minimumrepresents correlation caused by motion artifact, venous blood movementor another noise source, it may be ignored, and a local minimum may beselected instead.

Yet another method uses an ensemble average of the red and/or IR signalsover a much longer time to determine the pulse waveform shape, thenfitting shorter time averaged signals to that waveform shape. Basically,we replace the green light signal or ECG signal described above with along time average of red/IR.

As mentioned above, patient wearable devices hereof for implementing theabove aspects may be particularly useful for monitoring oxygensaturation in noisy regions for such measurements, for example, wherethere is significant local skin movement, such as the chest location.

One embodiment of the above aspect hereof is illustrated in FIGS. 6A-6C.In FIG. 6A, curve A (600) illustrates time varying output of thephotodiode of a device hereof for infrared (IR) reflection and curve B(602) illustrates time varying output of the photodiode of the devicefor red light reflection. In some embodiments, the skin is alternativelyilluminated by the red and IR LEDs to generate the signals collected bythe same photodiode. In FIG. 6B, time synchronized (i.e. timeconcordant) ECG data (or alternatively/additionally green PPG data orlong time average of red/IR as introduced above), illustrated by curve C(604), is added to the plot of FIG. 6A. Peak values in the ECG data(e.g. peaks 606 and 608) (or green PPG or long time average of red/IRdata, see above) may be used to define frames or intervals of pulseoximetry data. Additional consecutive frames or intervals are indicatedby 612 and 614, and further frames may be similarly determined. Inaccordance with this aspect, pulse oximetry data from a plurality offrames is collected. The magnitude of the plurality may vary widelydepending on particular applications. In some embodiments, the pluralityof frames collected is from 5 to 25; in one embodiment, a plurality isbetween 8 and 10 frames. Typically, frames or intervals of pulseoximetry data contain different numbers of signal samples. That is,output from the sensors may be sampled at a predetermined rate, such a32 samples per second. If the time between ECG (or green PPG or longtime average of red/IR) peaks varies, then the number of samples perframe will vary. In one embodiment, features in the ECG (or green PPG orlong time average of red/IR) data serving as the starting points of aframe are selected so that an associated peak in the pulse oximetry datais approximately in the mid-point, or center, of the frame, after whicha predetermined number of signal samples are recorded for each frame.Preferably in this embodiment, the predetermined number is selected tobe large enough to ensure that the pulse oximetry signal peak is roughlymid-frame. Sample values corresponding to time points above thepredetermined value are not used. After a plurality of frames of data iscollected, averages of the values at corresponding time points of theframes are computed. The values from such averages AC and DC componentsof the pulse oximetry data are determined and are then used to computerelative oxygen saturation by conventional methods, such as theratio-of-ratios algorithm, e.g. Cypress Semiconductor document No.001-26779 Rev A (Jan. 18, 2010). This basic procedure is summarized inthe flow chart of FIG. 6C. Frame size (in terms of number of samples) isdetermined (620). Values of samples at corresponding time points withineach frame are summed (622), after which average values for each timepoint are computed which, in turn, give the AC and DC components of IRand red and/or green light reflection with reduced noise. In someembodiments, values for these components can be used to compute oxygensaturation using conventional algorithms (626). Relative values foroxygen saturation may be converted into absolute values by calibratingthe measurements for particular embodiments. Calibration may be carriedout in controlled environments where individuals are exposed to varyingatmospheric concentrations of oxygen and measured oxygen saturationvalues are related to corresponding oxygen levels.

In addition to the above embodiment for comparing ECG and/or green PPGor long time average of red/IR signals with pulse oximetry signals, arange of other embodiments for such comparing is within thecomprehension of those of ordinary skill in the art. For example, inorder to find peaks of the AC component of pulse oximetry signals in thepresence of noise, features of the time concordant ECG signal that arelocated at characteristic times preceding and succeeding the pulseoximetry maximum and/or minimum values may be used to reliably determinethe pulse oximetry peak and minimum values when averaged over aplurality of heart beats (without the need to average all values of thepulse oximetry signal over the heart beats). For example, if, within aninterval, the R wave peak of an ECG signal characteristically preceded apulse oximetry signal maximum by x milliseconds and trailed a pulseoximetry signal minimum by y milliseconds, then the essentialinformation about the AC component of the pulse oximetry signal may beobtained by repeated measurements of just two values of pulse oximetrysignals.

In some embodiments, values for IR or red reflection measured by thephotodiode may be used to estimate depth and/or rate of respiration. InFIG. 6D, a curve (630) of Red or IR or green values over time isillustrated. In FIG. 6E, maximum values and minimum values of curve(630) are shown by dashed curves (632) and (634), respectively. Thedifference between the maximum and minimum values at a time point ismonotonically related to the depth of breath in an individual beingmonitored. Thus, as illustrated, breaths at time (636) are shallowerthan those at time (638). In some embodiments, depth of breath versustime may be computed and monitored in an individual. Over time, the rateof respiration can be evaluated from the curve of maximum and minimumvalues over time.

Moreover, moving from an appreciation of a derivation of a respirationwaveform from ECG R-S amplitude and/or R-R intervals, it has been foundthat a PPG and/or pulse oximeter as described herein can be used torelatively directly estimate a respiration waveform. As the chestexpands and contracts during breathing, the motion hereof shows up as awandering baseline artifact on the PPG signals. The respiration signalmay be isolated by filtering out the PPG data to focus on thebreathing/respiration signal. This may be particularly so with achest-mounted PPG.

In addition, a chest mounted accelerometer may also or alternatively beused to measure the respiration waveform, especially when the user islying on his/her back. As the chest expands and contracts, the chestaccelerates up and down (or transversely, or otherwise depending uponorientation), which can be measured by the accelerometer.

Either of these, PPG and/or accelerometer, devices and/or methods may beused discretely or in combination with each other and/or with theabove-described ECG-based respiration estimation technique. Usingmultiple methods may improve accuracy when compared to estimates basedon a single method. Respiration rate and depth may then be estimatedfrom the respiration signal using time-domain and/or frequency domainmethods.

In some implementations, heart beat timing (e.g., from ECG) and PPGsignals can be used to determine pulse transit time; i.e., the time forthe pressure wave to travel from the heart to other locations in thebody. Measurements of pulse transit time may then be used to determineor estimate blood pressure. Note, the heartbeat timing, ECG and/or PPGsignals may be generated by conventional or other to-be-developedmethods, systems or devices, or may be developed by wearable devicessuch as those otherwise described herein. I.e., the algorithms hereofmay be separately usable, as well as being usable in the wearablecardiac device.

As disclosed herein elsewhere, the PPG signals of several heart beatsmay be averaged by correlating each with a respective heartbeat. Theresult is a PPG frame where the heart rate-correlated PPG signal isreinforced while uncorrelated noise is diminished. Moreover, because thePPG frame is already correlated to the timing of the heartbeat, pulsetransit time may be estimated by determining the location of either thepeak or minimum with respect to either the beginning or end of the frameitself. This may be done either by finding the minimum and/or maximumsample(s), or by interpolating the signal to find points betweenmeasured samples. For example, interpolation may be done with aquadratic fit, a cubic spline, digital filtering, or many other methods.

The pulse transit time may also be estimated by correlating the PPGframe with a sample signal. By shifting the two signals with respect toeach other, the time shift resulting in the maximum correlation may bedetermined. If the sample signal is an approximation of the expected PPGframe, then the time shift with maximum correlation may be used todetermine the pulse transit time.

An exemplar methodology or algorithm herefor is described here and shownin the drawing FIGS. 7A, 7B and 7C. Initially, such a method 710 (whichincludes and/or is defined by parts 710 a, 710 b and/or 710 c) takes atleast one heartbeat (typical ECG) signal 712 and at least one PPG signal711 as input as shown in FIG. 7A, e.g. The heartbeat timinginformation/signal 712 is used to generate heartbeat timing informationby detecting the R-wave or other ECG feature from each beat; multipleECG signals (i.e. different leads from locations on the body) may beused to obtain a better estimate of the heartbeat timing information.The PPG 711 may use a single light wavelength or signals from multiplelight wavelengths. Using the corresponding heartbeat timing informationrelated to each PPG signal 711, each PPG signal 711 is segmented into“frames,” see PPG Frame 1, PPG Frame 2 and PPG Frame N in FIG. 7A, whereeach frame contains the PPG signal of a single wavelength for theduration of one corresponding beat of the heart.

Optionally, but, typically, a PPG signal quality estimate may also beperformed. An example of this is shown as method part 710 b in FIG. 7B.This estimate may consider the variance of the PPG signal, the estimatedsignal-to-noise ratio of the PPG signal, PPG signal saturation, patientmotion information from an accelerometer or gyroscope, an ECG orimpedance measurement noise estimate, or other information about the PPGsignal quality. Shown in FIG. 7B is an exemplar using accelerometersignal 713 in conjunction with PPG signal 711 to generate a PPG SignalQuality Value/Estimate 714. This signal quality estimate 714 may then beused in conjunction with the heartbeat timing information 712 togenerate the gain for each frame, see PPG Frame 1 Gain, PPG Frame 2 Gainand PPG Frame N Gain in FIG. 7B, where lower signal quality results in alower gain. To reduce computation time, the signal quality estimate 714may be omitted and a constant may be used for the gain information.

As shown in FIG. 7C, the gain information (PPG Frame 1 Gain, PPG Frame 2Gain and PPG Frame N Gain from FIG. 7B) may be used (here shown ascombined/manipulated) with the frame information (PPG Frame 1, PPG Frame2 and PPG Frame N from FIG. 7A) to create a weighted, n-samplemoving-average frame 715, where the PPG signal that is correlated withthe heartbeat timing is reinforced while the uncorrelated noise isreduced. The number of samples included in the frame (n) 715 may beadapted to reduce noise or decrease response time. The frames may beadditionally weighted by time in order to increase the contribution ofrecent or near-future frames with respect to frames that are furtheraway and potentially less-relevant. This additional weighting by timemay be implemented using an IIR or FIR filter.

Once the average frame 715 has been produced for a given instant intime, the pulse transit time 716 may be determined by finding the shiftin the frame signal with respect to the heartbeat. This may be donesimply by finding the sample index 717 where the signal is at a minimumor maximum and comparing it with the frame boundary (heartbeat timing)to determine the pulse transit time. For a more precise result, thesignal may be interpolated 718 using a spline or polynomial fit aroundthe minimum or maximum values, allowing the minimum or maximum to bedetermined with greater precision than the sample rate. Finally, theframe may be compared 719 to a reference frame template, where theaverage frame is shifted with respect to the template. The shift withthe highest correlation between the average frame and the templateindicates the transit time 716. This reference template may be apredetermined signal, or it may be allowed to adapt by using a long-termframe average with a known transit time.

Note, such methodologies may be used with PPG and heartbeat timinginformation obtained from a variety of sources, including but notlimited to conventional and/or to-be-developed technologies; or, may beobtained one or the other alone or together and/or together with qualitysignal (PPG variance, estimated PPG signal-to-noise ratio, PPG signalsaturation, patient motion accelerometer or gyroscope data, an ECG orimpedance measurement noise estimate, or other information about the PPGsignal quality) obtained from a wearable device and/or system asdescribed further hereinbelow.

Some further alternatives may include data transmission and/orinterpretation by local medical facilities, whether physician or doctoroffices or e.g., ICU/CCU (Intensive Care/Coronary Care Units).Accordingly, a device 100 hereof that will measure one or more of avariety of physiologic signals, possibly including electrocardiogram,photoplethysmogram, pulse oximetry and/or patient acceleration signalswill be placed on the patient's chest and held with an adhesive asdescribed herein. The device transmits the physiologic signalswirelessly or by wire (e.g., USB) to a nearby base station forinterpretation and further transmission, if desired. The wirelesstransmission may use Bluetooth, Wi-Fi, Infrared, RFID (Radio FrequencyIDentification) or another wireless protocol. The device may be poweredby wireless induction, battery, or a combination of the two. The device100 monitors physiological signals and/or collects data representativethereof. The collected data may then be transmitted wirelessly or bywire connection, in real time, to the nearby base station. The devicemay be wirelessly powered by the base station or by battery, removingthe need for wires between the patient and the station.

Relatedly and/or alternatively, patients or wearers may be monitoredwirelessly in a hospital, including an ICU (Intensive Care Unit) orother facility. As such, an ECG signal may be measured on a patientusing a small, wireless patch device hereof. The signal is thendigitized and transmitted wirelessly to a receiver. The receiverconverts the signal back to analog, such that it approximates theoriginal ECG signal in amplitude. This output is then presented to anexisting hospital ECG monitor through the standard electrode leads. Thisallows the patient to be monitored using existing hospitalinfrastructure without any lead wires necessarily connecting the patientto the monitor. Patient chest impedance may be measured as well,allowing the reconstructed signal to approximate the ECG signal not onlyin amplitude, but in output impedance as well. This can be used todetect a disconnected patch. The output impedance may be continuouslyvariable, or it may have discrete values that may be selected (e.g. onelow value for a connected device and one high value to signify the patchhas come loose). The impedance may also be used to signify problems withthe wireless transmission.

Other alternative implementations may include coupling one or multiplesensors mounted to the forehead of an infant. Initially, a method ofobtaining oxygen saturation data by mounting a device in the forehead ofan infant might be used as introduced. However, an expansion oralternative may include coupling oxygen saturation sensors with relativeposition and temperature sensors on the same forehead-mounted device.The combined data can be utilized to ascertain if an infant is in anydanger of suffocation due to a face-down position.

Thus, some of the alternative combinations hereof may include one ormore of: 1) medical grade adhesives (from many possible sources)selected for their ability to maintain in intimate contact with the skinwithout damaging it, for several days (up to, say 10 days or two weeksin some examples), as well as operability with different types ofsensors; 2) conductive electrodes or photo-sensitive detectors able tosupply electrical signals from the skin or from the photo-response ofcutaneous or subcutaneous tissues to photo-excitation; 3) amplifiers,microprocessors and memories, capable of treating these signals andstoring them; 4) power supply for the electronics hereof with stored orwith wirelessly accessible re-chargeability; 5) flex circuits capable oftying the above elements together within a flexible strip capable ofconforming to a cutaneous region of interest.

Examples of physiological parameters that may be subject to monitoring,recordation/collection and/or analyzing may include one or more of:electrocardiograms, photo responses of photo-excited tissues for e.g.,oxygen saturation of blood; pulse rates and associated fluctuations;indications of physical activity/acceleration. One or more of these maybe used in monitoring ambulatory cardiac outpatients over several daysand nights, which could thereby provide for recording, for post-testanalysis, several days' worth of continuous ECG signals together withsimultaneous recording of O2 saturation and an index of physicalexertion. Similarly, one or more of these may be used in monitoringambulatory pulmonary outpatients over several days and nights forrecording, for post-test analysis, O2 saturation together withsimultaneous recording of an index of physical activity. Alternativelyand/or additionally, one or more of these could be used for monitoringin-patients or other patients of interest, as for example neonates,wirelessly (or in some cases wired), whether in clinics, emergencyrooms, or ICUs, in some instances detecting the parameters of EKG, O2and/or physical exertion, but instead of storing them would transmitthem wirelessly to either a bedside monitor or a central stationmonitor, thus freeing the patient from attachment to physical wires. Inparticular, devices hereof may be adhered to the forehead of a neonatefor monitoring respiration and oxygen saturation. In furtheralternatives, devices hereof may be used to monitor respiration and ECGof patients suffering from sleep apnea.

An exemplary computer system or computing resources which may be usedherewith will now be described, though it should be noted that manyalternatives in computing systems and resources may be available andoperable within the reasonably foreseeable scope hereof so that thefollowing is intended in no way to be limiting of the myriad possiblecomputational alternatives properly intended within both the spirit andscope hereof.

Some of the implementations of the present developments include varioussteps. A variety of these steps may be performed by hardware componentsor may be embodied in machine-executable instructions, which may be usedto cause a general-purpose or special-purpose processor programmed withthe instructions to perform the steps. Alternatively, the steps may beperformed by a combination of hardware, software, and/or firmware. Assuch, FIG. 4 is an example of computing resources or a computer system400 with which implementations hereof may be utilized. According to thepresent example, a sample such computer system 400 may include a bus401, at least one processor 402, at least one communication port 403, amain memory 404, a removable storage media 405, a read only memory 406,and a mass storage 407. More or fewer of these elements may be used in aparticular implementation hereof.

Processor(s) 402 can be any known processor, such as, but not limitedto, an Intel® Itanium® or Itanium 2® processor(s), or AMD® Opteron® orAthlon MP® processor(s), or Motorola® lines of processors. Communicationport(s) 403 can be any of an RS-232 port for use with a modem baseddialup connection, a 10/100 Ethernet port, a Universal Serial Bus (USB)port, or a Gigabit port using copper or fiber. Communication port(s) 403may be chosen depending on a network such a Local Area Network (LAN),Wide Area Network (WAN), or any network to which the computer system 400connects or may be adapted to connect.

Main memory 404 can be Random Access Memory (RAM), or any other dynamicstorage device(s) commonly known in the art. Read only memory 406 can beany static storage device(s) such as Programmable Read Only Memory(PROM) chips for storing static information such as instructions forprocessor 402.

Mass storage 407 can be used to store information and instructions. Forexample, hard disks such as the Adaptec® family of SCSI drives, anoptical disc, an array of disks such as RAID, such as the Adaptec familyof RAID drives, or any other mass storage devices may be used.

Bus 401 communicatively couples processor(s) 402 with the other memory,storage and communication blocks. Bus 401 can be a PCI/PCI-X or SCSIbased system bus depending on the storage devices used.

Removable storage media 405 can be any kind of external hard-drives,floppy drives, IOMEGA® Zip Drives, Compact Disc--Read Only Memory(CD-ROM), Compact Disc-Re-Writable (CD-RW), Digital Video Dis-Read OnlyMemory (DVD-ROM).

The components described above are meant to exemplify some types ofpossibilities. In no way should the aforementioned examples limit thescope of the inventions hereof, as they are only exemplary embodiments.

Embodiments of the present inventions relate to devices, systems,methods, media, and arrangements for monitoring and processing cardiacparameters and data, inter alia. While detailed descriptions of one ormore embodiments of the inventions have been given above, variousalternatives, modifications, and equivalents will be apparent to thoseskilled in the art without varying from the spirit of the inventionshereof. Therefore, the above description should not be taken as limitingthe scope of the inventions, which is defined by the appended claims.

What is claimed is:
 1. A method, device and/or system as describedherein.
 2. A system or device or method of using a light pipe having oneor more light sources or LEDs and a barrier wall disposed therein forhealth monitoring.
 3. A system or device or method of using a light pipehaving one or more light sources or LEDs and a barrier wall disposedtherein; including disposing the barrier wall about the light sources orLEDs to disperse light in a desirable fashion for health monitoring. 4.A light pipe for health monitoring according to any of claims 1-3 havingone or both: one or more light sources or LEDs and a barrier walldisposed therein; and, one or more light sensors or photodiodes forhealth monitoring.
 5. A method, device or system for health monitoringaccording to any of claims 1-4 further comprising: one or more lightsources or LEDs; one or more light sensors or photodiodes; and, and abarrier wall disposed therein, in operative disposition separating theone or more light sources or LEDs from the one or more light sensors orphotodiodes; a light transmissive material having at least one of thelight sources or LEDs, at least one of the one or more light sensors orphotodiodes and the barrier wall disposed therewithin.
 6. A method,device or system for health monitoring according to any of claims 1-5further including that the light transmissive material is a light pipethat encapsulates either or both: the one or more light sources and theone or more sensors .
 7. A method, device or system according to claim 6further including the light transmissive material or light pipeencapsulating one or both the one or more light sources or the one ormore sensors, encapsulating by having substantially no air gaps betweenthe light transmissive material or light pipe encapsulating one or boththe one or more light sources or the one or more sensors, for one orboth: providing increased efficiency in light emission to the skin orcapturing otherwise lost photons.
 8. A method, device or systemaccording to any of claims 1-7 further including an external barrierwall.
 9. A method, device or system according to claim 8 the externalbarrier wall being used for collecting light.
 10. A method, device orsystem according to any of claims 1-9 including using the light pipe foroxygenation determination.
 11. A method, device or system according toclaim 10 further comprising: emitting light from one or more lightsources or LEDs; barring the light emitting from crossing the barrierwall; receiving reflected light from the light emitted from the lightsources or LEDs.
 12. A method, device or system according to claim 11further comprising one or more of: passing the light emitted from theone or more light sources into the skin of a subject; receivingreflected light from the subject; determining oxygenation from thereflected light.
 13. A method, device or system according to any ofclaims 10-12 further comprising one or more of: emitting light to theskin of the user by one or both of direct emission or reflection; and,collecting light by one or both of direct collection or reflection; thereflection being off the barrier wall or the external barrier wall. 14.A method of oxygenation determination, using a light pipe having one ormore light sources or LEDs and a barrier wall disposed therein.
 15. Amethod, device or system according to claims 1-14, using one or more ofred, InfraRed (IR), green, or using a weighted combination ofwavelengths.
 16. A method, device or system according to claims 1-15,comprising one or more of: the transmissive material being epoxy; thebarrier walls being one or the other of metal or plastic; the barrierwalls being either or both opaque or diffuse reflective to the one ormore wavelengths of light used; using one or more of red, InfraRed (IR),green, or using a weighted combination of wavelengths; the transmissivematerial having a substantially flat surface; a thin adhesive beingadhered to the surface of the transmissive material for adhering to theskin; the thin adhesive having a similar refractive index to thetransmissive material; and/or little or no air gap being presentedbetween the transmissive material and one or more of the skin, the lightsources and the sensors.
 17. A method of or device for oxygenationdetermination, the method using the device, the device having a lightpipe having one or more centrally disposed light sensors or photodiodesdisposed therein; the one or more light sensors or photodiodes arecentrally disposed relative one or more light sources or LEDs to sensereflected light emitted from the light sources or LEDs; the one or morelight sources or LEDs are peripherally disposed relative to the lightsensors or photodiodes.
 18. A method according to any of claims 1-17 theone or more light sensors or photodiodes being centrally disposedrelative one or more light sources or LEDs to sense reflected lightemitted from the light sources.
 19. A method according to any of claims1-18 the one or more light sources or LEDs being peripherally disposedrelative to the light sensors or photodiodes.
 20. A method according toclaims 1-19 comprising one or more of: two light sensors or photodiodesare disposed centrally relative to two or more light sources or LEDs;four light sensors or photodiodes are disposed centrally relative to twoor more light sources or LEDs; and, four light sensors or photodiodesare disposed centrally relative to four or more light sources or LEDs;the barrier wall being disposed between the light sensors or photodiodesand the light sources or LEDs.
 21. A device for monitoring aphysiological parameter, the device being adapted to be adhered to theskin of a subject for the physiological parameter monitoring; the devicecomprising: a substrate; and one or both of: a conductive sensorconnected to the substrate, and a combination of one or more pulseoximetry sensors connected to the substrate, and, one or more lightsources or LEDs for one or more wavelengths, and a barrier wall disposedtherebetween.
 22. A device according to claim 21, the one or more lightsensors or photodiodes being centrally disposed relative to the lightsources or LEDs.
 23. A device according to claim 21 or 22 or includingany of the methods, devices or systems of claims 1-20 the one or morepulse oximetry sensors and/or light sources or LEDs providing for afocused or controlled interrogation of a capillary bed in order toreduce local motion artifact effects.
 24. A method of oxygenationdetermination, using one or more centrally disposed light sensors orphotodiodes.
 25. A method according to claims 24 the one or morecentrally disposed light sensors or photodiodes being centrally disposedrelative one or more light sources or LEDs to sense reflected lightemitted from the light sources or LEDs.
 26. A method according to claim24 or 25 the one or more light sources or LEDs being peripherallydisposed relative to the light sensors or photodiodes.
 27. A methodaccording to claims 24-26, using red, InfraRed (IR), green, or using aweighted combination of wavelengths.
 28. A method according to claims24-27 comprising one or more of: two light sensors or photodiodes aredisposed centrally relative to two or more light sources or LEDs; fourlight sensors or photodiodes are disposed centrally relative to two ormore light sources or LEDs; and, four light sensors or photodiodes aredisposed centrally relative to four or more light sources or LEDs.
 29. Adevice for monitoring a physiological parameter, the device beingadapted to be adhered to the skin of a subject for the physiologicalparameter monitoring; the device comprising: a substrate; and one orboth of: a conductive sensor connected to the substrate, and acombination of one or more pulse oximetry sensors connected to thesubstrate, and, one or more light sources or LEDs for one or morewavelengths, the one or more light sources or LEDs being peripherallydisposed relative to the light sensors or photodiodes.
 30. A deviceaccording to claim 29 or including any of the methods of claims 24-28the one or more pulse oximetry sensors and/or light sources or LEDsproviding for interrogation of a wider area of capillary bed in order toreduce local motion artifact effects.
 31. A device for monitoring aphysiological parameter according to any of claims 24-30, the devicebeing adapted to be adhered to the skin of a subject for thephysiological parameter monitoring; the device comprising: a substrate;and one or both of: a conductive sensor connected to the substrate, andcircuitry for reducing errors caused by ambient light using a correlateddouble sampling technique; comprising: one or more light sensors; one ormore light sources or LEDs for one or more wavelengths, the one or morelight sources or LEDs being peripherally disposed relative to the lightsensors or photodiodes; first and second switches and; first and secondcapacitors, the first capacitor being in series with the light sensor,and the second capacitor being in parallel with the output, and thefirst and second switches being disposed between the output and groundto alternatively provide output or shunt to ground.
 32. A device, systemor method for monitoring a physiological parameter according to any ofclaims 1-31, the device, system or method being adapted to be adhered tothe skin of a subject for the physiological parameter monitoring; thedevice comprising: a substrate; and one or both of: a conductive sensorconnected to the substrate, and circuitry for reducing errors caused byambient light using a correlated double sampling technique; comprising:one or more light sensors; one or more light sources or LEDs for one ormore wavelengths; a barrier wall disposed between the one or more lightsensors or photodiodes and the one or more light sources or LEDs; firstand second switches and; first and second capacitors, the firstcapacitor being in series with the light sensor, and the secondcapacitor being in parallel with the output, and the first and secondswitches being disposed between the output and ground to alternativelyprovide output or shunt to ground.
 33. A device, system or methodaccording to claim 31 or 32 the one or more light sources or LEDs beingperipherally disposed relative to the light sensors or photodiodes. 34.A device, system or method according to either of claim 31, 32 or 33further including a resistor in parallel with the other circuitelements.
 35. A device, system or method according to claim 31, 32, 33or 34 the first capacitor being C1, the second capacitor is C2, thefirst switch being S1, the second switch being S2 and when the lightsources are turned off, and switch S1 is closed, and switch S2 is open;charge proportional to the noise signal accumulates on C1, and thenswitch S1 is opened and, then, the voltage on C1 is equal to the noisesignal voltage; and, next, the light signal may be measured; switch S2is closed, and charge is allowed to flow through C1 and C2 in series;and, then, S2 is opened, and the voltage is held on C2 until the nextmeasurement cycle when the whole process is repeated; and, if C1 is muchlarger than C2, nearly all the voltage will appear on C2, and thevoltage on C2 will be equal to the noise-free signal (s); or, otherwise,the voltage on C2 will be a linear combination of the previous C2voltage (p) and the noise-free signal: (C2*s+C1*p)/(C1+C2).
 36. Adevice, system or method according to claim 35 either one of: the effectis of applying a first-order, low-pass, IIR discrete-time filter to thesignal; or, if this filtering effect is not desired, the voltage on C2may be discharged to zero before the signal is measured each cycle, thesignal being held on C2 is: (C2*s)/(C1+C2).
 37. A device according toclaims 31-36; one or more of: a trans-impedance amplifier is used inplace of resistor R, a phototransistor in place of the light sensor, andFETs in place of the first and second switches; or the output may befollowed by one or more of additional buffering, amplification,filtering and processing stages.
 38. A method, device or systemaccording to any of claims 1-37 of measuring oxygen saturation in anindividual, the method comprising the steps of: measuring anelectrocardiogram signal over multiple heart beats; measuring one ormore pulse oximetry signals over multiple heart beats such that theelectrocardiogram signal and the one or more pulse oximetry signals arein time concordance over one or more heart beats; comparing a portion ofthe electrocardiogram signal and the one or more pulse oximetry signalsin time concordance over one or more heart beats to determine a constantcomponent and a primary periodic component of each of the one or morepulse oximetry signals; and determining oxygen saturation from theconstant components and primary periodic components of the one or morepulse oximetry signals.
 39. The method, device or system of claim 38said pulse oximetry signals including a reflective infrared signal and areflective red light signal.
 40. The method of claim 38 or 39 said stepof comparing including defining intervals of said pulse oximetry signalbased on characteristics of said electrocardiogram signal and averagingvalues of said pulse oximetry signal over a plurality of such intervals.41. The method of claims 38-40 said constant components and said primaryperiodic components of said pulse oximetry signals being determined fromsaid average values.
 42. The method of claims 38-41 saidelectrocardiogram signal including an R wave signal each with a peakvalue in each of said heart beats and said intervals being determinedwith respect to the peak values of the R wave signals.
 43. The method ofclaims 38-42 said electrocardiogram signal and said pulse oximetrysignal being measured from a chest location on said individual.
 44. Adevice, system or method according to any of claims 1-43 for reducingnoise in health monitoring including a wearable health monitoring devicehaving at least one sensor for health monitoring; the wearable healthmonitoring device having a composite adhesive having at least oneconductive portion applied adjacent the sensor; and, includingadaptations for the at least one sensor to have increased effectivenessin receiving signals with reduced noise; wherein the adaptations includea convex lens.
 45. A device according to claim 44 wherein the convexlens is adapted to be disposed in operative contact with awearer's/user's skin.
 46. A device according to claims 44-45 wherein theconvex lens is adapted to be disposed in operative contact with awearer's/user's skin at or adjacent the wearer's/user's forehead orchest.
 47. A device according to claims 44-46 wherein the convex lens isan encapsulant.
 48. A device according to claims 44-47 wherein theconvex lens encapsulant encapsulates the sensor.
 49. A device accordingto claims 44-48 wherein the convex lens encapsulant encapsulates thesensor and is in operative contact with the sensor not allowing aninterference airgap between the sensor and the encapsulant.
 50. A deviceaccording to claims 44-49 further comprising one or more LEDs whereinthe convex lens encapsulant encapsulates the one or more LEDs.
 51. Adevice according to claims 44-50 wherein the convex lens encapsulantencapsulates the one or more LEDs and is in operative contact with atleast one of the one or more LEDs not allowing an interference airgapbetween the at least one of the one or more LEDs and the encapsulant.52. A device according to claims 44-51 wherein the convex lens is one ormore of clear, colorless, silicone and medical grade silicone.
 53. Adevice according to claims 44-52 wherein the adaptations are used forpulse oximetry.
 54. A device according to claims 44-53 furthercomprising one or more functionalities including one or more of EKG, PPGand wearer acceleration.
 55. A device according to claims 44-54 furthercomprising one or more functionalities including one or both of drivenright leg and/or proxy driven right leg.
 56. A device according toclaims 44-55 further comprising a driven or proxy driven electrode on awearer chest or a wearer forehead.
 57. A device according to claim 56wherein the adaptation is disposed for and configured for maintainedindented operative contact with the wearer's/user's skin.
 58. A deviceaccording to claims 44-57 providing for transmission of LED wavestherethrough to the wearer's/user's skin without interferingtransmission thereinto.
 59. A device according to claim 58 providing forreception of reflected transmissions of LED waves therethrough from thewearer's/user's skin to the sensor without interfering transmissiontherethrough.
 60. A device according to claims 44-59 that is made frommedical grade silicone that is one or more of substantially clear,substantially colorless, substantially soft, substantially lowdurometer, tacky gel, or has very high-tack adhesives embedded on bothsides.
 61. A device according to claim 60 wherein the silicone withdouble-sided adhesive provides one or both conformance of the lens toone or both the electronic sensors and skin, or exhibition of motionartifact reduction by limiting movement between the skin-lens-sensorinterface.
 62. A device according to claim 60 or 61 that is speciallyconfigured such that it can be trapped between layers of the compositeadhesive strip of a wearable health monitoring device, with a raisedportion the size of the rectangular opening in the adhesive strip thatallows the lens to protrude slightly on the patient side of the adhesivestrip.
 63. A device, system or method according to any of claims 1-62for a health sensor; comprising a lens being configured for operativecontact with the wearer's/user's skin; and configured for providingnoninterfering light pipe transmission of energy waves therethrough. 64.A method of generating one or more of a pulse shape template or adataset representing a pulse shape using a method, system or deviceaccording to any of claims 1-63, the method comprising; using greenwavelengths, an ensemble average of green over approximately the sameamount of time as for either red or IR, an ensemble average of multiplewavelengths over approximately the same amount of time as for either redor IR, or an ensemble average of multiple wavelengths over significantlylonger than the amount of time as for either red or IR.
 65. A method fordetermining pulse oxygenation using a method, system or device accordingto any of claims 1-64; including: generating one or more of a firstpulse shape template or a dataset representing a first pulse shape,including using green wavelengths, an ensemble average of green overapproximately the same amount of time as for either red or IR, anensemble average of multiple wavelengths over approximately the sameamount of time as for either red or IR, or an ensemble average ofmultiple wavelengths over significantly longer than the amount of timeas for either red or IR; or a long time average of a single wavelengthof any color.
 66. A method for determining pulse oxygenation using amethod, system or device according to any of claims 1-65; comprising: a)detecting heart beats; using ECG, using green or another wavelength, orusing a weighted combination of wavelengths; b) generating one or moreof a first pulse shape template or a dataset representing a first pulseshape, including using green wavelengths, an ensemble average of greenover approximately the same amount of time as for either red or IR, anensemble average of multiple wavelengths over approximately the sameamount of time as for either red or IR, or an ensemble average ofmultiple wavelengths over significantly longer than the amount of timeas for either red or IR; or a long time average of a single wavelengthof any color; c) obtaining a red pulse shape template or datasetrepresenting same and an IR pulse shape template or dataset representingsame, and compare each of these to the first pulse shape above; and, d)correlating via linear regression between red ensemble average with thefirst pulse shape template or dataset to the IR ensemble average withthe first pulse shape or dataset, where the ratio of these correlationsis then used as the AC ratio for oxygen saturation.
 67. A methodaccording to any of claims 1-66 wherein colors other than green or redor IR are used.
 68. A method according to claim 67 wherein colorselection is limited only by minimal effectiveness in either signal tonoise ratio and/or reflectiveness related to oxygenation.
 69. A methodfor health monitoring using a method or device according to any ofclaims 1-68, the method comprising: determining from either or both auser's ECG and/or a first photoplethysmogram PPG signal and/or aweighted combination of wavelengths when heart beats occur; timeaveraging the first photoplethymogram PPG signal to generate a firstpulse shape template or dataset; time averaging each of two additionalphotoplethysmogram signals correlated to the beat locations; one of theadditional signals being red, the other additional signal being IR;generating ensemble averages for each of the red and IR signals;comparing each of the red and IR ensemble averages to the first pulseshape template or dataset; using a linear regression of each of the redand IR ensemble average-comparisons to the first pulse template ordataset to determine the linear gain factor between the two signals;determining from the gain factor the patient oxygen saturation.
 70. Amethod according to claim 69 wherein the first PPG signal is one or moreof: green, non-red; non-infrared and/or a weighted combination ofwavelengths.
 71. A method according to claims 69-70 wherein the twophotoplethysmogram signals include one or more or all of green, red andinfrared signals.
 72. A method according to any of claims 1-71 furthercomprising: recording the first PPG or ECG data in time-concordance withone or two or more additional photoplethysmographs of different lightwavelengths; detecting the heart beats in the first PPG or ECG signal,these heart beats allowing for definition of a frame ofphotoplethysmogram data for the time between two adjacent heart beats;averaging two or more of these frames together at each point in time tocreate an average frame for the time interval; wherein thephotoplethysmograph signal is reinforced by this averaging because thephotoplethysmogram is correlated with the heartbeat, and any motionartifact or other noise source that is uncorrelated in time with theheartbeat is diminished; interpreting the signal-to-noise ratio of theaverage frame as typically higher than that of the individual frames;using linear regression to estimate the gain between the two averageframe signals; estimating from this gain value one or more of the bloodoxygen saturation or other components present in the blood such ashemoglobin, carbon dioxide or others.
 73. A method according to any ofclaims 1-72 wherein the operations are repeated for additional lightwavelengths in order to estimate from the gain value one or more of theblood oxygen saturation or other components present in the blood such ashemoglobin, carbon dioxide or others.
 74. A method using a method ordevice according to any of claims 1-73 comprising: selecting a possiblegain value, multiplying the average frame signal by it, and determiningthe residual error with respect to an average frame of a differentwavelength; whereby the gain between red and infrared (IR) frame signalsare found by: generating one or more of green or other color PPG signalsor a long time average of red/IR; including the one or more of green orother color PPG signals or the long time average of red/IR with the redand IR frame signals to create two frames; averaging the two framestogether first to provide a signal with reduced noise; performing linearregression of the red versus combined with green or long time average ofred/IR and IR versus combined with green or long time average of red/IR;or linear regression of red versus green or long time average of red/IRand IR versus green or long time average of red/IR; or linear regressionby combining green or long time average of red/IR with each of red andIR and using the ratio of these results; and then finding the ratio ofthe two corresponding results.
 75. A method according to claim 74 fordetermining depth and/or rate of respiration.
 76. A method according toone of claims 74-75 wherein one or more of ECG data, PPG data, pulseoximeter data and/or accelerometer data is used to determine respirationrate and/or depth.
 77. A method according to claim 76 includinggenerating, using the one or more of ECG data, PPG data, pulse oximeterdata and/or accelerometer data, a respiration waveform.
 78. A methodaccording to claims 74-77 where Red or IR or green values over time areused.
 79. A method according to claims 74-78 including measuring IR orred or green reflection by the photodiode to estimate depth and/or rateof respiration.
 80. A method according to claims 74-79 where one or bothof maximum values and minimum values of a curve or waveform of the IR orred or green data represent the difference between the maximum andminimum values related to the depth of breath in an individual beingmonitored, and/or over time, the rate of respiration can be evaluatedfrom the curve of maximum and minimum values over time.
 81. A methodaccording to claims 74-80 using PPG signals.
 82. A method according toclaim 81 including generating the PPG signals when the chest expands andcontracts during breathing, the motion hereof presenting as a wanderingbaseline artifact on PPG signals.
 83. A method according to claims 81-82including isolating the respiration signal by filtering out the PPG datato focus on the breathing/respiration signal.
 84. A method according toclaims 81-83 wherein the PPG is chest-mounted.
 85. A device using themethod according to any of claims 1-84 wherein one or more of thesignals are obtained from one or more of: a wearable health monitoringdevice having: a substrate; a conductive sensor connected to thesubstrate, and a double-sided composite adhesive having: at least oneconductive adhesive portion, and at least one non-conductive adhesiveportion; the double-sided composite adhesive being attached to thesubstrate and the conductive sensor; the at least one conductiveadhesive portion being disposed in conductive communicative contact withthe conductive sensor, and being configured to be conductively adheredto the skin of the subject for conductive signal communication from thesubject to the conductive sensor.
 86. A method according to claim 74-85wherein any one or more of PPG and/or accelerometer, methods are useddiscretely or in combination with each other and/or with theabove-described ECG-based respiration estimation techniques.
 87. Amethod according to claim 74-86 wherein using multiple methods improvesaccuracy when compared to estimates based on a single method.
 88. Asystem using the device according to claim 87 further including acomputer.
 89. A device using the method of claims 87-88.
 90. A deviceaccording to claim 89 using a wearable health monitoring device.
 91. Amethod according to claims 74-90 using software and computer hardware todetermine the oxygen saturation.